The authors would like to acknowledge Ohio Cancer Research (OCR), OH, USA for funding this work as well as King Saud University (KSU), Riyadh, KSA for sponsoring the first author.&#160;Molecular weight of the fluorescent peptide sensor was measured using matrix assisted, laser desorption-ionization, time-of-flight (MALDI-TOF) mass spectrometry with assistance from the Campus Chemical Instrument Center Mass Spectrometry and Proteomics Facility at The Ohio State University.

1. Hydrogel components preparation
<ol>
	<li>Synthesize the fluorescent protease-degradable peptides as described elsewhere8, utilizing fluorescein as the fluorescent molecule and dabcyl as the quencher. Dissolve the peptide in DMSO to a concentration of 10 mM and store in a -80 &#176;C freezer in small (~30 &#181;L) aliquots to avoid repeated freeze-thaw cycles. 
	NOTE: These peptides can also be purchased commercially. This protocol requires a C-terminal cysteine in the peptide sequence to enable covalent incorporation into the hydrogel polymer network.</li>
	<li>Prepare 8 arm 40 kDa poly(ethylene glycol) amine (PEG)-norbornene (NB) as described17. Verify end group functionalization of greater than 90% using 1H NMR. Dissolve PEG-NB in sterile phosphate buffer saline (PBS) at 25% w/v and store in -80 &#176;C freezer in (~300 &#181;L) aliquots. 
	NOTE: PEG functionalized with norbornene can also be purchased commercially.</li>
	<li>Synthesize the photo-initiator lithium phenyl 2,4,6 trimethylbenzoylphosphinate (LAP) as described elsewhere18. Dissolve LAP in sterile water to a concentration of 68 mM and store in a -80 &#176;C freezer in (~300 &#181;L) aliquots. 
	NOTE: As an alternative, Irgacure (2-Hydroxy-4&#8242;-(2-hydroxyethoxy)-2-methylpropiophenone) can be used as the photo-initiator. LAP and Irgacure can be purchased commercially.</li>
	<li>Dissolve the MMP-degradable peptide crosslinker (KCGPQG&#8595;IWGQCK) and the cell adhesion peptide (CRGDS) in sterile water to a concentration of 200 mM and 100 mM respectively, and store them in a -80 &#176;C freezer in (~300 &#181;L and ~30 &#181;L) aliquots, respectively.</li>
</ol>
2. Assay media preparation
<ol>
	<li>Prepare the heat-inactivated, charcoal stripped fetal bovine serum (FBS) for the MMP assay: 
	NOTE: Proteases in FBS can produce a high background signal with the MMP assay; therefore, it is recommended to heat-inactivate and charcoal strip the FBS for the assay media.
	<ol>
		<li>Inactivate 100 mL of FBS by heating for 30 min at 55 &#176;C. 
		NOTE: 100 mL of FBS was utilized here for aliquoting and storage at -20 &#176;C for future use. Smaller volumes can be used as needed.</li>
		<li>Add 0.25% w/v of activated charcoal and 0.025% w/v of dextran to a small amount of FBS (approximately 5 mL) and stir until a slurry is formed. Then, add the rest of the FBS and stir for 30 min at 55 &#176;C.</li>
		<li>Centrifuge at 1,962 x g for 20 min at 4 &#176;C. Then transfer the supernatant to another vessel.</li>
		<li>Repeat step 2.1.2 but at 37 &#176;C followed by step 2.1.3. Sterilize the supernatant using a 0.45 &#181;m filter and then a 0.2 &#181;m filter.</li>
	</ol>
	</li>
	<li>Prepare assay media using media supplemented with 1% charcoal stripped FBS, 2 mM L-glutamine, 10 U/mL penicillin, 10 &#181;g/mL streptomycin. 
	NOTE: Media without phenol red is recommended because it has less fluorescence interference. Other additions to the assay media such as insulin, growth factors, etc. may be added as long as the absorbance and fluorescence spectrum peaks do not overlap with the sensor (494 nm/521 nm).</li>
	<li>Dilute bacterial collagenase enzyme type I at 10 and 1,000 &#181;g/mL in the assay media as a positive control.</li>
</ol>
3. Hydrogel preparation and cell encapsulation
<ol>
	<li>Prepare the hydrogel precursor solution.
	<ol>
		<li>Add the reagents to a 1.5 mL tube in the following order, vortexing after addition of each component: 20 mM 8 arm 40 kDa PEG-NB, 12.75 mM crosslinker MMP-degradable peptide, 17.8 mM NaOH, 1 mM CRGDS, 2 mM LAP, and 0.25 mM fluorogenic MMP-degradable peptide. 
		NOTE: Table 1 shows hydrogel precursor solution contents, stock concentrations, working concentrations, volume calculation formulas and the required volumes needed to make 120 &#181;L of hydrogel precursor solution, which is sufficient to conduct an experiment with 10 hydrogels. To account for loss of the hydrogel solution due to pipetting, increase the total volume by 20%. The commercial peptides are often supplied in an acidic hydrogen chloride solution; therefore, NaOH is added to achieve a final pH of 7. pH of the final solution should be confirmed by the user.</li>
		<li>Divide the hydrogel precursor solution into multiple 1.5 mL tubes, one tube per condition being tested. 
		NOTE: Several control conditions in which hydrogels are prepared without the addition of cells are suggested. For a negative control, to account for non-specific degradation of the fluorogenic sensor, one hydrogel condition can be incubated with the vehicle control or the experimental media alone if there are no treatment conditions. For a positive control and for calibration between experiments, hydrogels can be incubated with a protease known to cleave the fluorogenic sensor. For example, two concentrations of bacterial collagenase were used here.</li>
	</ol>
	</li>
	<li>Encapsulate cells in hydrogels.
	<ol>
		<li>Prepare a single cell suspension as appropriate for the cell type being used. For example, wash a 10 cm dish of A375 melanoma cells with 10 mL of PBS. Trypsinize cells using 0.05% trypsin and incubate at 37 &#176;C and 5% CO2 for 3 min. Count cells with a hemocytometer to determine total cell number.</li>
		<li>Centrifuge the cell solution at 314 x g for 3 min, aspirate culture media, then re-suspend cells in PBS at approximately three times the highest required seeding density for the experiment. For example, a cell suspension with a density of 21 x 106 cells was used here to achieve a final encapsulated density of 7 x 106 cells/mL.</li>
		<li>Count the cells again to ensure an accurate cell concentration.</li>
		<li>Add suspended cells and PBS to each tube of hydrogel precursor solution according to the required seeding density (0.25, 0.5, 1, 2, 3, 4, 5, 6, and 7 x 106 cells/mL in this example). Add PBS to conditions with no cells in lieu of suspended cells. 
		NOTE: All conditions should have the same final hydrogel precursor solution volume to ensure the ratio between the hydrogel components and PBS is constant. Do not vortex tubes that have cells in them, pipette up and down vigorously without creating bubbles in order to mix the precursor solution.</li>
		<li>Dispense 10 &#181;L of the hydrogel precursor solution into a sterile black round bottom 96-well plate, ensuring that the tip is centered in the middle of the each well while dispensing.</li>
		<li>Polymerize hydrogel precursor solution by exposing the plate to ultra violet (UV) light at 4 mW/cm2 for 3 min. 
		NOTE: The UV lamp (UVL-56 Handheld UV Lamp, UVP, Upland, CA) produces UV-A light at a long UV wavelength (365 nm), which does not affect cellular viability.</li>
		<li>Add 150 &#181;L of assay media to all wells except for the positive control conditions without encapsulated cells. To the positive controls, add 150 &#181;L of collagenase enzyme solution.</li>
		<li>Add 150 &#181;L of PBS to the outer wells of the plate to reduce evaporation during incubation.</li>
	</ol>
	</li>
</ol>
4. MMP and metabolic activity measurement
<ol>
	<li>Measure fluorescence immediately post-encapsulation to establish a baseline fluorescence measurement and ensure uniformity in hydrogel polymerization. Read the plate using a fluorescence microplate reader utilizing an opaque 96-well plate protocol with an area scan setting at 494 nm/521 nm (excitation/emission). This will be the 0 h read.</li>
	<li>Incubate plate in a humidified incubator at 37 &#176;C and 5% CO2 for 18 h.</li>
	<li>Add metabolic activity reagent (resazurin) at 1:10 (v/v) for each well.</li>
	<li>Incubate plate in a humidified incubator at 37 &#176;C and 5% CO2 for an additional 6 h. 
	NOTE: This incubation time may vary depending on cell type.</li>
	<li>Measure fluorescence at 24 h post-encapsulation. Read the plate using a fluorescence microplate reader utilizing an opaque 96-well plate protocol with an area scan setting at 494 nm/521 nm (excitation/emission) for MMP activity and 560 nm/590 nm (excitation/emission) for metabolic activity.</li>
</ol>

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The authors have nothing to disclose.

3D in vitro cell culture recapitulates many important aspects of the in vivo environment. However, 3D culture also makes assessing cell function and signaling challenging, as many biological assays require cellular retrieval and large numbers of cells. Therefore, the development of a simple 3D culture system that enables measurement of cellular function without further sample processing would greatly increase the utility of 3D culture systems. The 3D system described here can be adapted for a variety of different applica...

Three-dimensional (3D) culture systems often more closely recapitulate in vivo cellular responses than traditional two-dimensional (2D) culture systems, see several excellent publications1,2,3. However, utilizing 3D culture systems to measure cell function has been challenging due to the difficulty of cellular retrieval and further sample processing. This difficulty limits the measurement of many cellular functions in 3D culture systems. To overcome this difficulty, new techniques are needed that enable easy measurement of cell function within 3D environments. One way to address this need is the development of materials that not only support 3D cell culture but also incorporate sensors to measure cell function. For example, several hydrogel systems have incorporated fluorogenic protease cleavable moieties to enable visualization of protease activity within 3D environments4,5,6,7. While these systems were originally utilized for microscopic imaging, these systems can also be adapted for use in a global matrix metalloproteinase (MMP) activity assay using a standard plate reader, enabling facile measurement of a cell function in a 3D environment8.
MMPs, a superfamily of zinc proteases, play critical roles in normal tissue homeostasis and in many diseases. MMPs degrade and remodel extracellular matrix (ECM), cleave cell surface receptors and cytokines and activate other MMPs9,10. MMPs play critical roles in physiological processes such as wound healing and in diseases such as arthritis, atherosclerosis, Alzheimer&#39;s, and cancer (see reviews in 9,10,11). In cancer, high MMP expression levels are strongly correlated with cancer metastasis and poor prognosis12. Furthermore, MMPs contribute to tumor progression by promoting cancer cell invasion and migration, cellular processes that are inherently 3D phenomena13,14. Therefore, there is much interest in the ability to measure MMP activity in 3D culture in many contexts, including fundamental biological studies and drug screening assays.
PEG hydrogels are widely used for 3D cell culture due to their high water content, resistance to protein adsorption, and tunable nature. PEG hydrogels have been functionalized with a number of moieties to direct cell function, such as with ECM mimetic peptides like RGD, RLD, and IKVAV to facilitate cell adhesion, or direct tethering of growth factors such as transforming growth factor-&#946; (TGF-&#946;)15,16. More recently, PEG hydrogels have been functionalized with sensor peptides that enable measurement of cell function as well5,8. Specifically, the use of a PEG hydrogel system functionalized with a fluorogenic MMP-degradable peptide enabled measurement of cellular MMP activity in 3D cultures with a standard plate reader and required no further processing. These systems are also compatible with other measurements of cellular function, including metabolic activity. Here, a protocol is described for the measurement of MMP activity of cells cultured in a 3D PEG hydrogel functionalized with a fluorogenic MMP-degradable peptide, and results presented demonstrating the initial optimization experiments needed for use of this assay. Human melanoma cells (A375) were encapsulated in the fluorogenic hydrogels over a range of seeding densities to determine the appropriate seeding densities that are within the working range of the assay. After 24 h of encapsulation, MMP and metabolic activity were measured utilizing a standard microplate reader. Next, MMP activity was normalized to metabolic activity to determine the seeding densities within the linear range of the assay. Finally, intra-plate coefficient of variation percentages (% CV) were calculated between triplicates to reflect the reproducibility of the obtained results. This method enables simple and fast 3D cell culture, and easy measurement of protease activity with minimal sample processing.

<table border="0" cellpadding="0" cellspacing="0" style="width:723px;" width="723">
	<colgroup>
		<col />
		<col />
		<col />
		<col />
	</colgroup>
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">1X Phosphate Buffered Saline</td>
			<td style="width:268px;">Fisher Scientific</td>
			<td style="width:119px;">10-010-049</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Activated charcoal&#160;</td>
			<td style="width:268px;">Sigma-Aldrich</td>
			<td style="width:119px;">C3345</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Black round bottom 96-well plate</td>
			<td style="width:268px;">Brand-Tech</td>
			<td style="width:119px;">89093-600</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Cell adhesion peptide (CRGDS)</td>
			<td style="width:268px;">GenScript USA Inc.</td>
			<td style="width:119px;">custom made</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Collagenase enzyme type I&#160;</td>
			<td style="width:268px;">Life Technologies</td>
			<td style="width:119px;">17100-017</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Dextran</td>
			<td style="width:268px;">Sigma-Aldrich</td>
			<td style="width:119px;">D4876</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">DMEM High Glucose Media</td>
			<td style="width:268px;">Invitrogen</td>
			<td style="width:119px;">11965118</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Fetal bovine serum (FBS)&#160;</td>
			<td style="width:268px;">Seradigm</td>
			<td style="width:119px;">1500-500</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Fluorescence microplate reader&#160;</td>
			<td style="width:268px;">BioTek</td>
			<td style="width:119px;">Cytation 3</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Hemocytometer</td>
			<td style="width:268px;">Hausser Scientific Co.</td>
			<td style="width:119px;">3200</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">L-glutamine</td>
			<td style="width:268px;">Life Technologies</td>
			<td style="width:119px;">25030-081</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:272px;">MMP-degradable peptide crosslinker (KCGPQG&#8595;IWGQCK)</td>
			<td style="width:268px;">GenScript USA Inc.</td>
			<td style="width:119px;">custom made</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">NaOH</td>
			<td style="width:268px;">Fisher Scientific</td>
			<td style="width:119px;">S318500</td>
			<td style="width:64px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:272px;">Penicillin /streptomycin</td>
			<td style="width:268px;">Life Technologies</td>
			<td style="width:119px;">15140-122</td>
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			<td height="21" style="height:21px;width:272px;">Resazurin (Alamar Blue)</td>
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			<td style="width:119px;">DAL1100</td>
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			<td height="22" style="height:22px;width:272px;">UV light&#160;</td>
			<td style="width:268px;">UVP</td>
			<td style="width:119px;">95-0006-02</td>
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measuring global cellular matrix metalloproteinase and metabolic activity in 3d hydrogels

Three-dimensional (3D) cell culture systems often more closely recapitulate in vivo cellular responses and functions than traditional two-dimensional (2D) culture systems. However, measurement of cell function in 3D culture is often more challenging. Many biological assays require retrieval of cellular material which can be difficult in 3D cultures. One way to address this challenge is to develop new materials that enable measurement of cell function within the material. Here, a method is presented for measurement of cellular matrix metalloproteinase (MMP) activity in 3D hydrogels in a 96-well format. In this system, a poly(ethylene glycol) (PEG) hydrogel is functionalized with a fluorogenic MMP cleavable sensor. Cellular MMP activity is proportional to fluorescence intensity and can be measured with a standard microplate reader. Miniaturization of this assay to a 96-well format reduced the time required for experimental set up by 50% and reagent usage by 80% per condition as compared to the previous 24-well version of the assay. This assay is also compatible with other measurements of cellular function. For example, a metabolic activity assay is demonstrated here, which can be conducted simultaneously with MMP activity measurements within the same hydrogel. The assay is demonstrated with human melanoma cells encapsulated across a range of cell seeding densities to determine the appropriate encapsulation density for the working range of the assay. After 24 h of cell encapsulation, MMP and metabolic activity readouts were proportional to cell seeding density. While the assay is demonstrated here with one fluorogenic degradable substrate, the assay and methodology could be adapted for a wide variety of hydrogel systems and other fluorescent sensors. Such an assay provides a practical, efficient and easily accessible 3D culturing platform for a wide variety of applications.

The current assay was adapted from a previously developed and characterized 3D hydrogel culture system functionalized with a fluorogenic MMP cleavable sensor8. The fluorogenic MMP sensor used here consists of a peptide sequence, GPLAC(pMeOBzl)&#8595;WARKDDK(AdOO)C (&#8595; indicates the cleavage site) that was previously optimized for cleavage by MMP-14 and MMP-1119. The peptide is labeled with a fluorescent molecule (fluorescein) and a quen...

Watch this Scientific Journal Video about Measuring Global Cellular Matrix Metalloproteinase and Metabolic Activity in 3D Hydrogels at JoVE.com

Measuring Global Cellular Matrix Metalloproteinase and Metabolic Activity in 3D Hydrogels

Here, a protocol is presented for encapsulating and culturing cells in poly(ethylene glycol) (PEG) hydrogels functionalized with a fluorogenic matrix metalloproteinase (MMP)-degradable peptide. Cellular MMP and metabolic activity are measured directly from the hydrogel cultures using a standard microplate reader.

Three-dimensional (3D) cell culture systems often more closely recapitulate in vivo cellular responses and functions than traditional two-dimensional (2D) ...

measuring-global-cellular-matrix-metalloproteinase-metabolic-activity

Universidad de Cartagena UDEC

Research

JoVE Journal

Bioengineering

7.3K Views.  The Ohio State University. Here, a protocol is presented for encapsulating and culturing cells in poly(ethylene glycol) (PEG) hydrogels functionalized with a fluorogenic matrix metalloproteinase (MMP)-degradable peptide. Cellular MMP and metabolic activity are measured directly from the hydrogel cultures using a standard microplate reader.

Video: Measuring Global Cellular Matrix Metalloproteinase and Metabolic Activity in 3D Hydrogels

Planar Gradient Diffusion System to Investigate Chemotaxis in a 3D Collagen Matrix

The importance of cell migration can be seen through the development of human life. When cells migrate, they generate forces and transfer these forces to their surrounding area, leading to cell movement and migration. In order to understand the mechanisms that can alter and/or affect cell migration, one can study these forces. In theory, understanding the fundamental mechanisms and forces underlying cell migration holds the promise of effective approaches for treating diseases and promoting cellular transplantation. Unfortunately, modern chemotaxis chambers that have been developed are usually restricted to two dimensions (2D) and have complex diffusion gradients that make the experiment difficult to interpret. To this end, we have developed, and describe in this paper, a direct-viewing chamber for chemotaxis studies, which allows one to overcome modern chemotaxis chamber obstacles able to measure cell forces and specific concentration within the chamber in a 3D environment to study cell 3D migration. More compelling, this approach allows one to successfully model diffusion through 3D collagen matrices and calculate the coefficient of diffusion of a chemoattractant through multiple different concentrations of collagen, while keeping the system simple and user friendly for traction force microscopy (TFM) and digital volume correlation (DVC) analysis.

Cell migration is an important part of human development and life. In order to understand the mechanisms that can alter cell migration, we present a planar gradient diffusion system to investigate chemotaxis in a 3D collagen matrix, which allows one to overcome modern diffusion chamber limitations of existing assays.

The importance of cell migration can be seen through the development of human life. When cells migrate, they generate forces and transfer these forces to ...

Tunable Hydrogels from Pulmonary Extracellular Matrix for 3D Cell Culture

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung tissue from porcine, rat, or mouse, the tissue is perfused and submerged in subsequent chemical detergents to remove the cellular debris. Histological comparison of the tissue before and after processing confirms removal of over 95% of double stranded DNA and alpha galactosidase staining suggests the majority of cellular debris is removed. After decellularization, the tissue is lyophilized and then cryomilled into a powder. The matrix powder is digested for 48 hr in an acidic pepsin digestion solution and then neutralized to form the pregel solution. Gelation of the pregel solution can be induced by incubation at 37 &#176;C and can be used immediately following neutralization or stored at 4 &#176;C for up to two weeks. Coatings can be formed using the pregel solution on a non-treated plate for cell attachment. Cells can be suspended in the pregel prior to self-assembly to achieve a 3D culture, plated on the surface of a formed gel from which the cells can migrate through the scaffold, or plated on the coatings. Alterations to the strategy presented can impact gelation temperature, strength, or protein fragment sizes. Beyond hydrogel formation, the hydrogel stiffness may be increased using genipin.

This is a method to create a 3-dimensional cell culture scaffold from pulmonary extracellular matrix. Intact lung is processed into hydrogels that can support the growth of cells in three-dimensions.

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung ...

Production of Elastin-like Protein Hydrogels for Encapsulation and Immunostaining of Cells in 3D

Two-dimensional (2D) tissue culture techniques have been essential for our understanding of fundamental cell biology. However, traditional 2D tissue culture systems lack a three-dimensional (3D) matrix, resulting in a significant disconnect between results collected in vitro and in vivo. To address this limitation, researchers have engineered 3D hydrogel tissue culture platforms that can mimic the biochemical and biophysical properties of the in vivo cell microenvironment. This research has motivated the need to develop material platforms that support 3D cell encapsulation and downstream biochemical assays. Recombinant protein engineering offers a unique toolset for 3D hydrogel material design and development by allowing for the specific control of protein sequence and therefore, by extension, the potential mechanical and biochemical properties of the resultant matrix. Here, we present a protocol for the expression of recombinantly-derived elastin-like protein (ELP), which can be used to form hydrogels with independently tunable mechanical properties and cell-adhesive ligand concentration. We further present a methodology for cell encapsulation within ELP hydrogels and subsequent immunofluorescent staining of embedded cells for downstream analysis and quantification.

Recombinant protein-engineered hydrogels are advantageous for 3D cell culture as they allow for complete tunability of the polymer backbone and therefore, the cell microenvironment. Here, we describe the process of recombinant elastin-like protein purification and its application in 3D hydrogel cell encapsulation.

Two-dimensional (2D) tissue culture techniques have been essential for our understanding of fundamental cell biology. However, traditional 2D tissue ...

3D Analysis of Multi-cellular Responses to Chemoattractant Gradients

Various limitations of 2D cell culture systems have sparked interest in 3D cell culture and analysis platforms, which would better mimic the spatial and chemical complexity of living tissues and mimic in vivo tissue functions. Recent advances in microfabrication technologies have facilitated the development of 3D in vitro environments in which cells can be integrated into a well-defined extracellular matrix (ECM) and a defined set of soluble or matrix associated biomolecules. However, technological barriers have limited their widespread use in research laboratories. Here, we describe a method to construct simple devices for 3D culture and experimentation with cells and multicellular organoids in 3D microenvironments with a defined chemoattractant gradient. We illustrate the use of this platform for analysis of the response of epithelial cells and organoids to gradients of growth factors, such as epidermal growth factor (EGF). EGF gradients were stable in the devices for several days leading to directed branch formation in breast organoids. This analysis allowed us to conclude that collective gradient sensing by groups of cells is more sensitive vs. single cells. We also describe the fabrication method, which does not require photolithography facilities nor advanced soft lithography techniques. This method will be helpful to study 3D cellular behaviors in the context of the analysis of development and pathological states, including cancer.

We describe a method to construct devices for 3D culture and experimentation with cells and multicellular organoids. This device allows analysis of cellular responses to soluble signals in 3D microenvironments with defined chemoattractant gradients. Organoids are better than single cells at detection of weak noisy inputs.

Various limitations of 2D cell culture systems have sparked interest in 3D cell culture and analysis platforms, which would better mimic the spatial and ...

Pancreatic Tissue-Derived Extracellular Matrix Bioink for Printing 3D Cell-Laden Pancreatic Tissue Constructs

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary complications. However, islet transplantation still has several limitations such as the low viability of transplanted islets due to poor islet engraftment and hostile environments. In addition, the insulin-producing cells differentiated from human pluripotent stem cells have limited ability to secrete sufficient hormones that can regulate the blood glucose level; therefore, improving the maturation by culturing cells with proper microenvironmental cues is strongly required. In this article, we elucidate protocols for preparing a pancreatic tissue-derived decellularized extracellular matrix (pdECM) bioink to provide a beneficial microenvironment that can increase glucose sensitivity of pancreatic islets, followed by describing the processes for generating 3D pancreatic tissue constructs using a microextrusion-based bioprinting technique.

Decellularized extracellular matrix (dECM) can provide suitable microenvironmental cues to recapitulate the inherent functions of target tissues in an engineered construct. This article elucidates the protocols for the decellularization of pancreatic tissue, evaluation of pancreatic tissue-derived dECM bioink, and generation of 3D pancreatic tissue constructs using a bioprinting technique.

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary ...

A Human 3D Extracellular Matrix-Adipocyte Culture Model for Studying Matrix-Cell Metabolic Crosstalk

The extracellular matrix (ECM) plays a central role in regulating tissue homeostasis, engaging in crosstalk with cells and regulating multiple aspects of cellular function. The ECM plays a particularly important role in adipose tissue function in obesity, and alterations in adipose tissue ECM deposition and composition are associated with metabolic disease in mice and humans. Tractable in vitro models that permit dissection of the roles of the ECM and cells in contributing to global tissue phenotype are sparse. We describe a novel 3D in vitro model of human ECM-adipocyte culture that permits study of the specific roles of the ECM and adipocytes in regulating adipose tissue metabolic phenotype. Human adipose tissue is decellularized to isolate ECM, which is subsequently repopulated with preadipocytes that are then differentiated within the ECM into mature adipocytes. This method creates ECM-adipocyte constructs that are metabolically active and retain characteristics of the tissues and patients from which they are derived. We have used this system to demonstrate disease-specific ECM-adipocyte crosstalk in human adipose tissue. This culture model provides a tool for dissecting the roles of the ECM and adipocytes in contributing to global adipose tissue metabolic phenotype and permits study of the role of the ECM in regulating adipose tissue homeostasis.

We describe a 3D human extracellular matrix-adipocyte in vitro culture system that permits dissection of the roles of the matrix and adipocytes in contributing to adipose tissue metabolic phenotype.

The extracellular matrix (ECM) plays a central role in regulating tissue homeostasis, engaging in crosstalk with cells and regulating multiple aspects of ...

Controlled Strain of 3D Hydrogels under Live Microscopy Imaging

External forces are an important factor in tissue formation, development, and maintenance. The effects of these forces are often studied using specialized in vitro stretching methods. Various available systems use 2D substrate-based stretchers, while the accessibility of 3D techniques to strain soft hydrogels, is more restricted. Here, we describe a method that allows external stretching of soft hydrogels from their circumference, using an elastic silicone strip as the sample carrier. The stretching system utilized in this protocol is constructed from 3D-printed parts and low-cost electronics, making it simple and easy to replicate in other labs. The experimental process begins with polymerizing thick (&#62;100 &#956;m) soft fibrin hydrogels (Elastic Modulus of ~100 Pa) in a cut-out at the center of a silicone strip. Silicone-gel constructs are then attached to the printed-stretching device and placed on the confocal microscope stage. Under live microscopy the stretching device is activated, and the gels are imaged at various stretch magnitudes. Image processing is then used to quantify the resulting gel deformations, demonstrating relatively homogenous strains and fiber alignment throughout the gel&#8217;s 3D thickness (Z-axis). Advantages of this method include the ability to strain extremely soft hydrogels in 3D while executing in situ microscopy, and the freedom to manipulate the geometry and size of the sample according to the user&#8217;s needs. Additionally, with proper adaptation, this method can be used to stretch other types of hydrogels (e.g., collagen, polyacrylamide or polyethylene glycol) and can allow for analysis of cells and tissue response to external forces under more biomimetic 3D conditions.

The presented method involves uniaxial stretching of 3D soft hydrogels embedded in silicone rubber while allowing live confocal microscopy. Characterization of the external and internal hydrogel strains as well as fiber alignment are demonstrated. The device and protocol developed can assess the response of cells to various strain regimes.

External forces are an important factor in tissue formation, development, and maintenance. The effects of these forces are often studied using specialized ...

Measuring 3D In-vivo Shoulder Kinematics using Biplanar Videoradiography

The shoulder is one of the human body's most complex joint systems, with motion occurring through the coordinated actions of four individual joints, multiple ligaments, and approximately 20 muscles. Unfortunately, shoulder pathologies (e.g., rotator cuff tears, joint dislocations, arthritis) are common, resulting in substantial pain, disability, and decreased quality of life. The specific etiology for many of these pathologic conditions is not fully understood, but it is generally accepted that shoulder pathology is often associated with altered joint motion. Unfortunately, measuring shoulder motion with the necessary level of accuracy to investigate motion-based hypotheses is not trivial. However, radiographic-based motion measurement techniques have provided the advancement necessary to investigate motion-based hypotheses and provide a mechanistic understanding of shoulder function. Thus, the purpose of this article is to describe the approaches for measuring shoulder motion using a custom biplanar videoradiography system. The specific objectives of this article are to describe the protocols to acquire biplanar videoradiographic images of the shoulder complex, acquire CT scans, develop 3D bone models, locate anatomical landmarks, track the position and orientation of the humerus, scapula, and torso from the biplanar radiographic images, and calculate the kinematic outcome measures. In addition, the article will describe special considerations unique to the shoulder when measuring joint kinematics using this approach.

Biplane videoradiography can quantify shoulder kinematics with a high degree of accuracy. The protocol described herein was specifically designed to track the scapula, humerus, and the ribs during planar humeral elevation, and outlines the procedures for data collection, processing, and analysis. Unique considerations for data collection are also described.

The shoulder is one of the human body's most complex joint systems, with motion occurring through the coordinated actions of four individual joints, ...

Fragmenting Bulk Hydrogels and Processing into Granular Hydrogels for Biomedical Applications

Granular hydrogels are jammed assemblies of hydrogel microparticles (i.e., &#34;microgels&#34;). In the field of biomaterials, granular hydrogels have many advantageous properties, including injectability, microscale porosity, and tunability by mixing multiple microgel populations. Methods to fabricate microgels often rely on water-in-oil emulsions (e.g., microfluidics, batch emulsions, electrospraying) or photolithography, which may present high demands in terms of resources and costs, and may not be compatible with many hydrogels. This work details simple yet highly effective methods to fabricate microgels using extrusion fragmentation and to process them into granular hydrogels useful for biomedical applications (e.g., 3D printing inks). First, bulk hydrogels (using photocrosslinkable hyaluronic acid (HA) as an example) are extruded through a series of needles with sequentially smaller diameters to form fragmented microgels. This microgel fabrication technique is rapid, low-cost, and highly scalable. Methods to jam microgels into granular hydrogels by centrifugation and vacuum-driven filtration are described, with optional post-crosslinking for hydrogel stabilization. Lastly, granular hydrogels fabricated from fragmented microgels are demonstrated as extrusion printing inks. While the examples described herein use photocrosslinkable HA for 3D printing, the methods are easily adaptable for a wide variety of hydrogel types and biomedical applications.

This work describes straightforward, adaptable, and low-cost methods to fabricate microgels with extrusion fragmentation, process the microgels into injectable granular hydrogels, and apply the granular hydrogels as extrusion printing inks for biomedical applications.

Granular hydrogels are jammed assemblies of hydrogel microparticles (i.e., &#34;microgels&#34;). In the field of biomaterials, granular hydrogels have ...

Cellular Affinity of Particle-Stabilized Emulsion to Boost Antigen Internalization

The cellular affinity of micro-/nanoparticles is the precondition for cellular recognition, cellular uptake, and activation, which are essential for drug delivery and immune response. The present study stemmed from the observation that the effects of charge, size, and shape of solid particles on cell affinity are usually considered, but we seldom realize the essential role of softness, dynamic restructuring phenomenon, and complex interface interaction in cellular affinity. Here, we developed poly-lactic-co-glycolic acid (PLGA) nanoparticle-stabilized Pickering emulsion (PNPE) that overcame the shortcomings of rigid forms and simulated the flexibility and fluidity of pathogens. A method was set up to test the affinity of PNPE to cell surfaces and elaborate on the subsequent internalization by immune cells. The affinity of PNPE to bio-mimetic extracellular vesicles (bEVs)-the replacement for bone marrow dendritic cells (BMDCs)-was determined using a quartz crystal microbalance with dissipation monitoring (QCM-D), which allowed real-time monitoring of cell-emulsion adhesion. Subsequently, the PNPE was used to deliver the antigen (ovalbumin, OVA) and the uptake of the antigens by BMDCs was observed using confocal laser scanning microscope (CLSM). Representative results showed that the PNPE immediately decreased frequency (&#916;F) when it encountered the bEVs, indicating rapid adhesion and high affinity of the PNPE to the BMDCs. PNPE showed significantly stronger binding to the cell membrane than PLGA microparticles (PMPs) and AddaVax adjuvant (denoted as surfactant-stabilized nano-emulsion [SSE]). Furthermore, owing to the enhanced cellular affinity to the immunocytes through dynamic curvature changes and lateral diffusions, antigen uptake was subsequently boosted compared with PMPs and SSE. This protocol provides insights for designing novel formulations with high cell affinity and efficient antigen internalization, providing a platform for the development of efficient vaccines.

To rationally design efficient adjuvants, we developed poly-lactic-co-glycolic acid nanoparticle-stabilized Pickering emulsion (PNPE). The PNPE possessed unique softness and a hydrophobic interface for potent cellular contact and offered high-content antigen loading, improving the cellular affinity of the delivery system to antigen-presenting cells and inducing efficient internalization of antigens.

The cellular affinity of micro-/nanoparticles is the precondition for cellular recognition, cellular uptake, and activation, which are essential for drug ...