Patent Application
20150086993
The present invention relates to the construction of in vitro tissue models, more specifically methods and devices for in vitro culturing of bone tissue models comprising osteocyte 3D network.
As master regulators of homeostatic bone remodeling, mature osteocytes embedded in the three-dimensional (3D) lacuna-canalicular network (3D-LCN) structure are known to sense local compressive strain and initiate strain-dependent new bone formation by osteoblasts, utilizing cytokines such as sclerostin and Dkk1 expressed by the osteocytes as major signaling molecules. For example, mouse ulna loading studies elegantly show that higher strain regions of the ulna bone result in less production of sclerostin and increased local osteogenesis at those regions.
Despite these important understandings, a significant challenge remains for in vivo studies of osteocytes due to the difficulty of accessing deeply embedded osteocytes in bone tissues. As yet, there is currently no in vitro model that is capable of reproducing the physiological phenotype and mechanotransduction function of osteocytes for routine use in biomedical research and preclinical drug evaluation. This problem may occur for several reasons: (1) the phenotypic function of primary osteocytes harvested from animal bones cannot be maintained during conventional two-dimensional (2D) culture; (2) commonly used osteocyte-like cell lines such as MLO-Y4 are sufficiently altered so that they do not express sclerostin at detectable levels; and (3) in vitro differentiation of osteoblasts into 3D mature osteocytes with network formation and sclerostin expression has not been realized.
A novel in vitro bone tissue model with a reconstructed 3D osteocyte network could be extremely useful for studying fundamental biological mechanisms associated with osteocytes as master regulators of bone remodeling. The model can be preliminarily validated by reconstructing the bone-like tissue with a 3D mouse osteocyte network and comparing it to the in vivo mouse data. Furthermore, the comparison could provide significant new insights and promote new developments in culturing primary human osteocytes and extending the model's capability for simulating human bone remodeling, including osteocyte-regulated bone formation and bone resorption. Operated at a microfluidic scale, such a human 3D bone tissue model may complement (or possibly replace) animal testing in preclinical evaluation of authentic human tissue response to drugs (e.g., sclerostin antibodies that are being actively pursued for treating the approximately 10 million osteoporosis patients in the U.S., and for treating bone metastases, which presently cause about 350,000 deaths every year in the U.S.
In a first aspect, the present invention comprises a method of culturing osteocytes in a microfluidic chamber. In an embodiment, a suspension of pre-osteocytes is mixed with microbeads, and the mixture is deposited in a microfluidic chamber to form a bed of closely-packed microbeads with pre-osteocytes distributed among the microbeads. In an embodiment, the bed is perfused with a culture medium such that the pre-osteocytes differentiate and develop into osteocytes. In an embodiment, the cultured osteocytes along with the close-packed microbeads form a bone-like tissue. In an embodiment, the microbeads have diameters such that interstitial spaces between adjacent microbeads may be occupied by no more than one of the cells. In an embodiment, the embedded cells form 3D network emulating the LCN structure in native bone tissues. In an embodiment, a drug or other biologically-active substance is included in the culture medium, and the effect of the drug or other biologically-active on the development of the bone-like tissue is assessed. In an embodiment, the microbeads include biphasic calcium phosphate. In an embodiment, the cells include pre-osteocytes and/or osteocytes.
In a second aspect, the present invention comprises a microfluidic device having a chamber defining an opening and having an inlet spaced away from the opening, a semipermeable barrier closing said opening, an impermeable substrate across the semipermeable barrier, and an outlet for collecting liquid passing through the semipermeable barrier and conveying the liquid away from the microfluidic device. In an embodiment, the microfluidic device includes a liquid-permeable bed of microbeads and cells within the chamber.
For a more complete understanding of the present invention, reference is made to the following detailed description of exemplary embodiments considered in conjunction with the accompanying drawings, in which:
Embodiments of the present invention provide a biomimetic approach to emulate the physiologically-relevant microscale dimensions of three-dimensional (“3D”) lacunocanalicular structures (“3D-LCN”) that can be subjected to long-term perfusion culture. In this approach, osteocytes and/or osteocyte precursors are assembled with microbeads within the physical confines of a microfluidic culture chamber. In the microfluidic environment, the model of the present invention allows compressive loading to be applied to the reconstructed 3D osteocyte networks. The microfluidic environment also allows for the reproduction of the compressive strain-sclerostin expression relationship as a means of validating the functionality of the reconstructed 3D osteocyte network. Devices and methods according to embodiments of the present invention may be used to assess the effectiveness of bioactive substances on the growth or regeneration of bone tissues, or as part of integrated microfluidic systems to assess the safety and effectiveness of medical treatments. Suitable integrated microfluidic systems are disclosed in U.S. Patent Application Publication No. 2013/0143230 by Tolias et al., which is incorporated by reference herein in its entirety.
Osteocytes are the most abundant cells (more than 90%) that reside in mineralized extracellular matrix (“ECM”) cavities in bones. Such cavities are referred to as “lacunae”. As illustrated in
As illustrated in
The diameter of BCP microbeads used in the reconstructed tissue of embodiments of the present invention can be selected according to the osteocyte diameter and intercellular space that varies between species. For close-packed microbeads, the diameter of interstitial sites (d′) and the distance between interstitial sites (d) are:
d′≈0.4D Eq. 1
d=D Eq. 2
where D is the diameter of microbeads. Therefore, for mouse osteocyte cells (e.g., cell lines MLO-Y4 or MLO-A5) with a typical diameter of 8-10 μm, microbeads with diameters in the range of about 20 to about 25 μm may be selected to: (1) allow a single cell to be placed within the interstitial site that is sufficiently large (d′=8-10 μm), for occupation by one cell, but too small for occupation by more than one cell; (2) mitigate the proliferation of the cell placed in the interstitial site due to the physical confinement by the interstitial site; and (3) control the cell-to-cell distance to that of d (i.e., about 20-25 μm). In an embodiment, BCP is chosen as the microbead material, since BCP is known to facilitate mineral deposition by early and late osteoblastic cells through controlled release of calcium ions. Other suitable microbead materials may be preferred by others having ordinary skill in the relevant arts.
In a general embodiment of a method according to the present invention, a suspension of pre-osteocyte cells is suspended and mixed thoroughly with microbeads. A portion of the mixture is placed on the semipermeable barrier of a microfluidic culture device, such as the microfluidic culture devices 42, 66 of
Exemplary embodiments of the present invention are presented below. These embodiments do not limit the scope of the invention, which includes numerous modifications and variations of the exemplary embodiments, as will be recognized by those having ordinary skill in the relevant arts.
In an exemplary embodiment, spray-driedisintered BCP microbeads (CaP Biomaterials, LLC, East Troy, Wis.) were sieved to a size range according to the size and intercellular space of the subject osteocytes in authentic bones. For mouse osteocytic cell line MLO-Y4, with typical diameters of 8 to 10 μm, microbeads of 20 to 25 μm in diameter were used. The microbeads were then coated with a collagen solution. In the present exemplary embodiment, the microbeads were coated using a 10 mg/mL collagen/hexafluoroisopropanol solution. After sufficient time had elapsed to evaporate the hexafluoroisopropanol solvent (e.g., approximately one hour), the microbeads were washed with phosphate buffered saline (PBS).
The MLO-Y4 cells were cultured and expanded in collagen-coated flasks using alpha-minimum essential medium (α-MEM, Invitrogen, Carlsbad, Calif.), supplemented with 2.5% fetal bovine serum (FBS, ATCC), 2.5% calf serum (CS, ATCC) and 1% antibiotic solution (penicillin-streptomycin, MP Biomedicals, Solon, Ohio). The cells were then maintained at about 37° C., about 5% CO2 and over 90% humidity, and subcultured when they reach about 80% confluence.
The cellular tissue was then allowed to reconstruct. After tissue reconstruction, the cells were suspended and mixed with the coated microbeads. In the present exemplary embodiment, the cells were suspended using trypsin, then mixed with BCP microbeads to final concentrations of 1×107 cells/mL and 1×107 microbeads/mL (i.e., cell/microbead ratio of 1:1). Referring again to
Following the aforesaid perfusion, the cells were further cultured within the microfluidic chamber by perfusion with a growth medium. In the present exemplary embodiment, growth culture was carried out for 3 days in α-MEM supplemented with 5% FBS, since FBS is known to help maintain the osteocytic phenotype of the cells.
After the growth culture, the resulting tissue construct of microbeads and cultured cells appeared as a monolith (see, e.g., the tissue construct 82 of
Referring to
Cell viability in the tissue was determined by removing the cells from the tissue construct, staining the cells and measuring cell viability. In this exemplary embodiment, this process was carried out utilizing live/dead cell viability dye (Invitrogen) as stain, and quantitatively measuring cell viability through flow cytometry. These results were performed under triplication. As illustrated in
Osteocyte-specific gene Pdpn, which regulates osteocyte process growth, was examined using quantitative real-time polymerase chain reaction techniques (PCR). As illustrated in
This second exemplary embodiment demonstrates the 3D morphological development, extracellular matrix production, and differentiation of early osteocytes of the MLO-A5 line entrapped in the tissue/microbeads construct during 3 weeks of perfusion culture in the microfluidic culture chamber.
Spray-dry/sintered BCP microbeads were purchased from CaP Biomaterials LLC (East Troy, Wis.). According to the supplier, the microbeads were composed of 68% of hydroxyapatite and 32% of β-tricalcium phosphate. The microbeads were sieved to a size range of 20-25 μm and coated with collagen type I (Sigma-Aldrich) using 10 mg/mL collagen/hexafluoroisopropanol solution for 2 hours. They were then washed with phosphate buffered saline (PBS) three times and stored for further use.
The MLO-A5 post-osteoblast/pre-osteocyte cell line was a kind gift from Professor Lynda Bonewald (University of Missouri-Kansas City). Cells were maintained in collagen-coated flasks in α-MEM (Gibco) supplemented with 5% (v/v) fetal bovine serum (FBS, ATCC), 5% (v/v) calf bovine serum (CBS, ATCC) and 1% (v/v) penicillin-streptomycin (P/S, MP Biomedicals, Solon, Ohio) at 37° C. and 5% CO2, and subcultured once until they reached about 80% confluence. Cells from passages 2 to 9 were used according to the exemplary culture and characterization methods described below.
Microfluidic 3D Culture of MLO-A5 Cells with BCP Microbeads
MLO-A5 cells were suspended using trypsin and mixed thoroughly with BCP microbeads at concentrations of 1×107 cells/mL and 1×107 microbeads/mL to produce a cell/microbead ratio of 1:1. 10 μL of the mixture was placed using a micropipette onto the top of the membrane in each chamber of the microfluidic device of
Pressure Drop Measurement across the Tissue Models
As shown in
At Day 3, the microfluidic devices were disassembled to harvest the cultured tissues. Cells were trypsinized to detach them from the BCP microbeads and stained with the live/dead cell vitality dye (Invitrogen) following the manufacturers protocol. Cell viability was quantitatively measured by flow cytometry (Beckman Coulter FC500). A minimum of 10,000 events were acquired and analyzed using the CXP cytometer analysis software (Beckman Coulter).
At Day 3 and Day 21, the 3D tissues were harvested and fixed with 4% formaldehyde/PBS solution. They were then dehydrated in sequential ethanol solutions with increasing concentrations from 50% to 100%. Some samples were embedded in glycol methacrylate and cut into histological sections of 20 μm thickness. Several sections were stained with 4′,6-diamidino-2-phenylindole (DAPI, Sigma-Aldrich) to examine cell distribution under fluorescent microscopy (Nikon Ti), while other sections were stained with either toluidine blue (Sigma) or hematoxylin & eosin (H&E, Sigma) to examine cell morphology and extracellular matrix production under an optical microscope. A portion of the dehydrated samples were gold-coated and directly visualized under a scanning electron microscope (SEM, Zeiss Auriga FIB-SEM, Zeiss NTS, Peabody, Mass.).
The remaining samples were further examined by microcomputed tomography (microCT, Scanco μCT 35, Bassersdorf, Switzerland) system. The scans were performed in air using 3.5 μm voxel size, 45 KVp, 0.36 degrees rotation step (180 degrees angular range), 400 ms exposure and 1 averaging frame per view. The Scanco μCT software (HP, DECwindows Motif 1.6) was used for viewing of images and 3D image reconstruction. After 3D image reconstruction, volumes were segmented using a global threshold of 0.5 mg/cc. Directly measured bone volume fraction (BV/TV), tissue mineral density (TMD), trabecular number (Tb.N), trabecular thickness (Tb.Th), trabecular separation (Tb.Sp), connectivity density, and structure model index (SMI) were calculated for the 3D tissue samples cultured for 3, 10, and 21 days.
Total RNA from the MLO-A5 cells cultured in the tissue/microbeads constructs was isolated at Day 3, 10 and 21, using an RNA Mini kit (Ambion) following the manufacturer's protocol. 1 μg of the total RNA from each sample was used for cDNA synthesis. Briefly, (1) 3 μL of 10 mM Oligo-dT solution (Sigma) was added to 16.5 μL of the RNA solution, heated at 75° C. for 5 min and cooled on ice; (2) a total of 30 μL reaction solution was: (1) constituted by further adding 1 μL RNasin Ribonuclease Inhibitor (Promega Corp, Madison, Wis.), 1.5 μL dNTp (Promega), 2 μL Reverse Transcriptase (Promega), and 6 μL Reverse Transcriptase Buffer (Promega), (2) incubated at 37° C. for 1.5 h, (3) stopped at 95° C. for 3 min, and (4) kept on ice. A final volume of the 20 μL reaction solution that consists of 2 μL of the cDNA template, 1 μL of primer, 10 μL of PCR master mix (Taqman), and 7 μL of DEPC-treated water was prepared for quantitative RT-PCR assay (StepOnePlus, Applied Biosystems). All primers were purchased from Taqman. Amplification conditions were as follows: 95° C., 20 s; 95° C., 1 s, 60° C., 20 s, 40 cycles. The relative expression of targeted genes was normalized to the GAPDH gene and gene expression level of cells at Day 0 using the 2-ΔΔCt method except Sost, for which 2-ΔCt method was used. The primers used are summarized in Table 1. 2D cultures were performed as controls using a 96-well plate that was pre-coated with a layer of BCP microbeads.
All samples in the assays of live/dead viability, MicroCT and qPCR were performed in triplicates. One-way ANOVA followed by the Tukey's multiple comparison tests was performed for pressure drop measurement, MicroCT and qPCR results. Student's t-test was used to analyze the result of qPCR between 2D and 3D culture. p<0.05 was considered statistically significant.
The culture medium flow rate of 1 μL/min was used, resulting in an average residence time of about 30 seconds through the 200 μm-thick tissue samples, to mimic interstitial flow from Haversian canals to the deepest regions of osteons. The pressure drop across the 3D microbeads without cells and the local average wall shear stress on the microbead surface were estimated using the modified Kozeny equation (Eqs. 1 and 2) developed by Riefler et al. and applying the tube bundle theory (Eqs. 3 and 4):
where ΔP is the pressure drop across the thickness of the structure (Δx≈200 μm), ε is the void fraction (about 0.3 for close packing), D is the mean diameter of microbeads (22.5 μm), μ is the viscosity of the medium, ν0 is the superficial velocity, Q is the volumetric velocity of culture medium, A is the cross-sectional area of the culture chamber, τw is the wall shear stress on the microbead surface, and AVS is the volumetric surface of the whole structure. Using these equations, ΔP and τw were estimated to be about 3.2 Pa and about 0.1 Pa, respectively, for the closed packed microbeads assembly.
In comparison, the measured ΔP value was 8.2 Pa for closely packed BCP particles in the absence of cells (see
A mechanically integrated structure of MLO-A5 cells and microbeads was obtained after 3 days of culture. The tissue samples were dismantled by trypsin and the released cells were collected for flow cytometry. As shown in
Histological analysis of the 3D tissues stained with DAPI showed that cells occupied interstitial sites of microbeads, and were distributed throughout the 200 μm-thick samples. The interstitial occupancy by the cells was estimated to be about 80% based on cross-sectional images. Cross-sectional views with toluidine blue staining and top SEM views showed that the osteocyte-like cells attached to the microbeads, grew processes and extended their processes to neighboring cells to form gap-junctions in all directions. Taken together, the results show that the 3D cellular network could be formed upon 3 days of culture.
3D Tissue Characteristics after 21-Day Culture
Over the 21-day culture period, the cells produced significant amounts of ECM as previously described and became further embedded, as shown by H&E staining and SEM imaging. Also, SEM imaging showed that the cells became more elongated and stellate in their shape and formed tens of processes per cell, exhibiting characteristic morphological features of osteocytes. Moreover, the cells that were embedded in the interstitial space did not proliferate.
The Micro CT images of the tissue samples confirmed that tissues mineralized and became denser and more connective over time. As summarized in Table 2, the bone volume ratio (BV/TV) at Day 10 and Day 21 were 10% and 17% greater than at Day 3, respectively. Meanwhile, all other calculated parameters showed similar and consistent trends with respect to increased density and connectivity of the tissue samples.
Osteoblast-specific genes (Alpl and Col1a1), osteoblast-to-osteocyte transition genes (E11 and Dmp1), gap-junction component protein gene (Cox43), and mature osteocyte-specific gene (Sost) were examined as a function of culture time. As shown in
The expressions of early osteocyte-specific genes (E11 and Cox43) showed remarkable differences between 2D and 3D cultures (
The late osteocyte-specific gene expression, Sost, was not detected in both 2D and 3D at Day 3 (
Several iterative experiments were performed with primary mouse osteocytes, using the reconstruction strategy established with MLO-A5 cells, discussed in Example 2, above. Long bones of 20-week-old mice were harvested, cleaned, diced into small pieces of 1-2 mm long and 0.5 mm wide, and digested nine times using collagenase solutions. Cells that were immediately released from the bone pieces (“digested cells”) did not adhere and were dead by Day 7. In contrast, cells that were gradually migrated out of the bone chips over 2 days (“outgrown cells”) were viable over a few weeks. There were initially round-shaped, but became adherent and began to develop processes by Day 4. At this time, 88% of these cells were stained as Alp-negative and Sost-positive, and were therefore identified as osteocytes. After Day 7, it appeared that some of the outgrown cells were re-differentiating to become osteoblastic and proliferative. Outgrown cells were released from well plates using trypsin and then assembled with BCP microbeads into the perfusion culture device. About 30% of the interstitial spaces were observed to be occupied by the cells. The results clearly suggest the feasibility of reconstructing the 3D cellular network with primary osteocytes.
It should be understood that the embodiments of the invention described herein are merely exemplary and that a person skilled in the art may make many variations and modifications without departing from the spirit and scope of the invention. All such variations and modifications are intended to be included within the scope of the invention as defined in the appended claims.
The present application claims the benefit of U.S. Provisional Patent Application No. 61/880,305, filed on Sep. 20, 2013, the disclosure of which is incorporated by reference herein in its entirety.
Development of the present invention was sponsored in part by the National Science Foundation (“NSF”) under Grant Numbers DMR-1005902 and DMR-1409779, and the National Institute of Arthritis and Musculoskeletal and Skin Diseases of the National Institutes of Health (“NIH-NIAMS”) under Award Number R21AR065032. The U.S. Government may have certain rights to the disclosed invention.
| Number | Date | Country | |
|---|---|---|---|
| 61880305 | Sep 2013 | US |
