3D Microtissues for Injectable Regenerative Therapy and High-throughput Drug Screening

Summary

This protocol describes the fabrication of elastic 3D macroporous microcryogels by integrating microfabrication with cryogelation technology. Upon loading with cells, 3D microtissues are generated, which can be readily injected in vivo to facilitate regenerative therapy or assembled into arrays for in vitro high-throughput drug screening.

Abstract

To upgrade traditional 2D cell culture to 3D cell culture, we have integrated microfabrication with cryogelation technology to produce macroporous microscale cryogels (microcryogels), which can be loaded with a variety of cell types to form 3D microtissues. Herein, we present the protocol to fabricate versatile 3D microtissues and their applications in regenerative therapy and drug screening. Size and shape-controllable microcryogels can be fabricated on an array chip, which can be harvested off-chip as individual cell-loaded carriers for injectable regenerative therapy or be further assembled on-chip into 3D microtissue arrays for high-throughput drug screening. Due to the high elastic nature of these microscale cryogels, the 3D microtissues exhibit great injectability for minimally invasive cell therapy by protecting cells from mechanical shear force during injection. This ensures enhanced cell survival and therapeutic effect in the mouse limb ischemia model. Meanwhile, assembly of 3D microtissue arrays in a standard 384-multi-well format facilitates the use of common laboratory facilities and equipment, enabling high-throughput drug screening on this versatile 3D cell culture platform.

Introduction

Traditional cell culture on flattened two-dimensional (2D) surfaces, such as a culture dish or multi-well plates, can hardly elicit cell behaviors close to their native states. Accurate recapitulation of native cellular microenvironments, which comprise of various cell types, extracellular matrices and bioactive soluble factors in three-dimensional (3D) architectures^1,2,3,4, is essential to construct biomimicking tissues in vitro for applications in tissue engineering, regenerative medicine, fundamental biology research and drug discovery^5,6,7,8,9.

In lieu of 2D cell culture, 3D cell culture is widely used to advance biomimetic micro-architectural and functional features of cells cultured in vitro. A popular 3D cell culture method is to aggregate cells into spheroids^7,8,9,10. Cellular spheroids could be injected to injured tissues with enhanced cellular retention and survival in comparison to injection of dispersed cells. However, non-uniform spheroid sizes and inevitable mechanical injury imposed on cells by fluid shear force during injection lead to poor cell therapeutic effects^11,12,13. Similarly, the inherent non-uniformity during aggregation of spheroids has made their translation to 3D cell-based high-throughput drug screening challenging¹⁰.

Another method for 3D cell culture is achieved with the assistance of biomaterials, which typically encapsulates cells in aqueous hydrogels or porous scaffolds. It allows for greater flexibilities in constructing 3D architectures. For therapy, cells encapsulated in bulk scaffolds are usually delivered to animal body via surgical implantation, which is invasive and traumatic, hence restricting its wide translation to bedside. On the other hand, aqueous hydrogels enable minimally invasive therapy by injecting cells suspended in hydrogel precursor solution into animal bodies, allowing in situ gelation via thermo-, chemical or enzymatic crosslinking¹¹. However, as cells are delivered whilst the hydrogel precursors are still in an aqueous state, they are also exposed to mechanical shear during injection. Not only so, chemical or enzymatic crosslinking during in situ gelation of hydrogel could also impose damage to cells within. For drug screening, biomaterial-assisted cell cultures face problems with uniformity, controllability and throughput. Using hydrogels, cells are typically involved during gelation, by which the process may affect cell viability and function. Gelation during cell seeding also hampers usage by most high-throughput equipment, since the hydrogel may need to be kept on ice to prevent gelation before cell seeding, and the hydrogel might jam dispensing tips, which are usually very thin to ensure accuracy for high-throughput screening. Pre-formed scaffolds could potentially separate biomaterial fabrication procedures from cell culture, however most scaffold-based products are available as bulk materials with relatively lower throughput¹⁴.

To overcome some of the shortcomings of current 3D culture methods, we have developed a microfabrication-cryogelation integrated technology to fabricate an off-the-shelf and user-friendly microcryogel array chip¹⁵. In this protocol, gelatin is selected to exemplify the microcryogel fabrication technique as it is biocompatible, degradable, cost-effective, and no further modification is required for cell attachment. Other polymers of natural or synthetic sources could also be used for fabrication, depending on the application. Via this technology, we can fabricate miniaturized and highly elastic microcryogels with controllable size, shape and layout. When loaded with a variety of cell types, 3D microtissues could be formed for various applications. These unique features enable desired injectability, cell protection and site-directed retention after injection in vivo for enhanced therapeutic effects. Not only so, the microcryogels could be further processed to form 3D microtissue arrays that are compatible with common laboratory equipment and instruments to realize high-throughput cell culture for versatile drug screening and other cellular assays. Herein, we shall detail the fabrication process of microcryogels and its post-treatment as individual 3D microtissues or 3D microtissue arrays for two important applications, cell therapy and drug screening, respectively^10,15.

Protocol

Animal experiments followed strict protocol approved by the Animal Ethics Committee on the Center of Biomedical Analysis, Tsinghua University. Under approval of Ethics Committee, human adipose tissue was obtained from Department of Plastic Surgery of Peking Union Hospital with informed consent from the patients.

1. Fabrication of 3D Microcryogels

1. Design and fabrication of microstencil array chips
   1. Use a commercial software to design arrays of specific geometries, such as circles, ellipses, triangles or clovers¹⁴, depending on subsequent application.
      NOTE: Refer to section 2 of the protocol for regenerative medicine and section 3 of protocol for drug screening for design details.
   2. Import the design into the laser engraving software accompanying the laser engraving machine. Using the laser settings according to the factory recommendations for the laser engraving machine, laser-engrave the imported design onto Poly (methymethacrylate) (PMMA) sheets.
   3. Wash the microstencil array chips with deionized water to clean debris from the laser engraving. Dry the microstencil array chips at 60 °C. Store in a sealed bag at room temperature for months.
2. Fabrication of microcryogel array chips
   1. Place 4 microstencil array chips on the sample tray and insert into the plasma cleaner. Close the door of the cleaner and turn on the vacuum pump for 2 min, then turn on the maximum RF power (18 W) to treat the microstencil array chips in the plasma cleaner for 3 min at room temperature to increase hydrophilicity.
   2. Add 0.06 g gelatin to 1 mL deionized water to form 6% (wt/vol) gelatin precursor solution (enough to make 5 chips). Warm at 60 °C in a water bath to dissolve adequately. Incubate on ice for 5 min.
   3. Add 3 µL of glutaraldehyde into the gelatin precursor solution to a final concentration of 0.3%. Mix thoroughly.
   4. Pipette 200 µL precursor solution with glutaraldehyde onto the upper surface of the microstencil array chip.
      NOTE: 200 µL is sufficient for a 75 mm × 25 mm chip regardless of design. Increase the amount proportionally when surface area of chip is increased.
   5. Manually distribute the solution evenly over the chip by scraping back and forth with a bent glass rod 2 to 3 times.
      NOTE: Each micro-well on the microstencil chip can be filled with precursor solution due to their hydrophilic nature after plasma treatment.
   6. Immediately place the precursor-solution-filled array chip in a -20 °C freezer for 16 h for cryogelation.
   7. Adjust the lyophilizer to -40 °C for 30 min. Place the array chips after cryogelation in the lyophilizer and lyophilize the array chips for 2 h in vacuum.
      NOTE: Gelatin microcryogels with interconnected macropores are formed because ice formed during cryogelation sublimes in the lyophilizer.
   8. Proceed to section 2 for treatment of critical limb ischemia (CLI) and section 3 for high-throughput drug screening.

2. Harvesting Individual Microcryogels to Form Injectable 3D Microtissues for Treatment of CLI

1. Harvesting individual microcryogels
   1. Design arrays (75 mm × 25 mm) of 600 circles, each with 400 µm diameter, in commercial software for injectable 3D microtissue construction. Use PMMA of 300 µm thickness for fabrication of microstencil array chip as detailed in section 1.1.
   2. Fabricate microcryogel array chips as in section 1.2.
   3. Fabricate a PDMS Ejector Pin array with the same design as in step 2.1.1 by standard soft lithography^16,17.
   4. Overlay the microcryogel array chip on top of the PDMS Ejector Pin array, aligning each microcryogel with an ejector pin on the array. Press the microcryogel array chip towards the ejector pin array to push the microcryogels out of the microwells with the protruding pins on the PDMS ejector pin array to harvest individual microcryogels.
   5. Harvest the microcryogel into water and collect them with the aid of cell strainers. Use one strainer to collect microcryogels from one chip (i.e., 600 microcryogels).
   6. Wash microcryogels with 0.1 M NaBH₄ on ice for 20 min to quench any uncross-linked aldehyde residue. Use 5 mL of 0.1 M NaBH₄ per chip. Discard NaBH₄ and wash with 5 mL deionized water for 3 to 5 times, 15 min each time.
   7. Discard water from the cell strainer and gather microcryogels into one cluster per cell strainer and place one cluster in one 35-mm Petri dish using a curved tweezer. Add 50 - 70 µL deionized water to each cluster and cover the lid of the Petri dish. Gently tap the Petri dish on the tabletop to level out all microcryogels, so that no microcryogels are lying on top of another microcryogel to form a monolayer of microcryogels on the surface of the Petri dish.
   8. Freeze the harvested microcryogels at -20 °C for 4 to 16 h before lyophilizing them for 2 h(see step 1.2.7).Store microcryogels in a vacuum at room temperature until further use.
2. Characterization of microcryogels
   1. Evaluate the pores of the microcryogels by scanning electron microscopy (SEM) imaging.
      1. Immobilize the harvested and lyophilized microcryogels onto a sample holder by double-side adhesive tape and coat with gold with a sputter coater for 90 s, before imaging by SEM¹¹. Evaluate and analyze the distribution of diameters of pores in the microcryogel from seven different SEM images using image analysis software.
   2. Weigh one cluster of 600 lyophilized microcryogels in a 35-mm Petri dish for the weight of dried gelatin microcryogels (GMs). Add 60 µL deionized water to the cluster of lyophilized microcryogels and wait for 30 s for microcryogels to fully absorb water and swell. Weigh the swollen microcryogels.
      1. Determine the equilibrium swelling ratio and porosity of microcryogels, as the ratio of weight of swollen microcryogels to that of dried gelatin microcryogels and the ratio of weight of held water in microcryogels to that of hydrated microcryogels, respectively¹³.
   3. Measure injectability of microcryogels using a programmable syringe pump integrated with a digital force gauge¹⁴.
      1. Stain 600 pieces of microcryogels by Trypan blue and suspend in 600 µL 15% gelatin solution to achieve homogeneous distribution. Load 1 mL microcryogel suspension in 1 mL syringe. Inject the mixture through a 27-gauge needle attached to the 1 mL syringe using a programmable syringe pump at flow rate of 1 mL/min.
      2. Monitor real-time injection force by digital force gauge testing and plot the force-time curve. After injection, observe the integrity of microcryogels under a microscope.
         NOTE: GMs suspended in 15% (wt/vol) gelatin solution can be smoothly injected and remained intact after injection.
   4. Characterize the degradability of microcryogels.
      1. First, measure the weight of one cluster of 600 lyophilized microcryogels in a 35-mm Petri dish as the dry weight. Then, immerse 600 lyophilized microcryogels in 2 mL 0.025% (vol/vol) Trypsin/EDTA.
      2. Collect microcryogels from the solution using a cell strainer at different time points (i.e., 10, 20, 30, 40, 50, 60, and 70 min). Wick away excess solution with a tissue. Measure the weight of microcryogels at different time points and calculate the degradation degree, as the ratio of weight of microcryogel at a certain time point to that of microcryogel at time zero.
3. Autoloading of cells into microcryogels to form 3D microtissues
   1. Sterilize microcryogels from step 2.1.8 by ethylene oxide sterilization system with 12 h gas exposure followed by 12 h degassing under vacuum.
   2. Choose human adipose-derived mesenchymal stromal cells (hMSCs) for treatment of mouse ischemic hindlimb. Isolate cells by following procedures as previously reported¹⁸.
   3. Culture hMSCs in the growth medium containing 2% fetal bovine serum (FBS), 10 ng/mL epidermal growth factor (EGF), 10 ng/mL platelet-derived growth factor bb (PDGF-bb), 1X insulin transferrin selenium (ITS), 10^-8 M dexamethasone, 10^-4 M ascorbic acid 2-phosphate, 100 U/mL penicillin, and 100 µg/mL streptomycin in DMEM/F12. Passage the cells at the ratio of 1:3 when confluent. Use cells of passage 3 to 5 in the following experiments.
   4. Harvest hMSCs with trypsin and quantify the cell number using a Fuchs-Rosenthal counting chamber and resuspend to a density of 8 x 10⁶ cells/mL in hMSCs growth medium.
   5. Pipette 60 µL hMSCs suspension onto the monolayer of 600 microcryogels with diameter of 400 µm in a 35-mm dish from section 2.1. Cells are automatically absorbed into the porous micro-structures of the microcryogels.
   6. Maintain in a humidified chamber and incubate at 37 °C for 2 h to allow cells to attach. After 2 h of incubation, add 2 mL culture medium. Change the medium every 2 days. Culture hMSCs-loaded microcryogels for 2 days to form 3D microtissues.
   7. After 2 days culturing, pipette 100 hMSCs-loaded microcryogels per well on a 96-well plate, add 120 µL of resazurin working solution prepared according to the manufacturer's instruction into each well. Incubate for 2 h at 37 °C.
      1. Detect fluorescence of resazurin metabolized by viable cells in a microplate reader with an excitation light wavelength of 560 nm and emission light wavelength of 590 nm. Establish a standard curve of cell number vs. fluorescence using hMSCs to interpolate cell number from fluorescence intensity for future experiment according to the kit protocol¹³.
   8. Assess number of hMSCs in microcryogels from day 0 to day 4 using resazurin as described in step 2.3.7 from day 0 to day 4.
   9. Stain cells in microcryogels with 1:500 dilution of Calcein AM and 1:250 dilution of Propidium Iodide (known as live/dead staining) in phosphate buffered saline (PBS) and observe under fluorescence microscope or confocal fluorescence microscope.
4. Injection of 3D microtissues in vivo for treatment of CLI in mouse model
   1. Establish critical hindlimb ischemia of female BALB/c nude mice as reported^11,19 to determine the therapeutic effect of 3D microtissue-based therapy.
   2. Transfer the microtissues from step 2.3.6 using a 5-mL pipette into a cell strainer and filter away the culture medium.
   3. Resuspend the hMSCs-loaded 3D microtissues in 15% gelatin solution, at a density of 100 microcryogels per 100 µL solution.
   4. Before surgery, sterilize surgical tools by autoclave and perform surgery in an animal operating room in an Animal Facility Center.
   5. Place the mouse into the anesthesia induction chamber containing 1-3% isoflurane in 100% oxygen at a flow rate of 1 L/min. Apply erythromycin on the eyes of the mouse to prevent drying. Through a 1-cm-long skin incision, ligate the femoral artery and its branches with 5-10 silk sutures and excise¹⁹.
   6. Inject indocyanine green (ICG) (0.1 mL of 100 µg/mL) through the tail vein injection to monitor blood flow. Perform ICG fluorescence imaging using a fluorescence imaging system (here, homemade system) in the reflectance geometry¹¹.
   7. Intramuscularly inject microtissues into three sites of the gracilis muscle around the artery incision using a 1 mL syringe with a 23-gauge needle.
   8. After surgery, keep the mouse warm with a heated pad in the recovery cage. Inject subcutaneously meloxicam to relieve the pain and monitor continuously until awake.
   9. After 28 days, monitor the therapeutic efficacy of 3D microtissue-treated limb by fluorescence imaging¹¹.
       Note: Inject subcutaneously meloxicam to relieve the pain when the mouse showed spontaneous limb amputation.
   10. Euthanize mice with carbon dioxide after completion of experiments.
       NOTE: Here, euthanasia with carbon dioxide was performed according to strict protocol approved by the Animal Ethics Committee on the Center of Biomedical Analysis, Tsinghua University.

3. Assembly of Microtissue Array Chip for High-throughput Drug Screening

1. Assembly of microcryogel array for on-chip cell culture
   1. Modify the design in section 1.1 according to conventional multi-well plate dimensions, i.e., for 384-multi-well format, design an array of 16 × 24 wells (row by column), each of 2 mm diameter and 4.5 mm center-to-center spacing.
   2. Laser engrave onto a 500 µm thick PMMA sheet as described in section 1.1.
   3. Fabricate microcryogels as described in section 1.2 using the 384-multi-well array chip obtained from step 3.1.2. This microcryogel-containing array is designated as the microcryogel array chip.
   4. Wash the microcryogel array chip with 50 mL 0.1 M NaBH₄ to quench any residual aldehyde uncross-linked, then repeatedly rinse with 50 mL deionized water for 3 times, 2 h each time.
   5. Discard the water, freeze the microcryogel array chip at -20 °C for 4 to 16 h before lyophilizing according to step 1.2.7.
   6. Modify the 384-multi-well array design in step 3.1.1 to contain 16 × 24 wells, each of 3 mm diameter and 4.5 mm center-to-center spacing.
   7. Remove one side of the backing from a sheet of ultra-thin (10 µm) biocompatible double-sided adhesive tape and paste it to one side of a piece of 3-mm-thick PMMA sheet. Laser engrave the design from step 3.1.4 onto this 3-mm-thick PMMA sheet according to section 1.1. This array is designated as the reservoir array.
   8. Align the microcryogel array chip with the reservoir array chip and adhere together tightly to assemble the 3D microcryogel array chip for on-chip cell culture. Sterilize by ultra-violet radiation for 1 h.
   9. Store 3D microcryogel array chips in vacuum at room temperature for further experiments.
2. Drug screening on 3D microtissue arrays
   1. Fill up a wet box with 25 mL sterile de-ionized water to serve as a humidity chamber for cell culture. Pre-heat in a humidified 5% CO₂ incubator to 37 °C.
   2. Harvest non-small-cell lung cancer cells (NCI-H460) and hepatocellular carcinoma cells (HepG2) from the tissue culture plates according to standard protocol and re-suspend in culture media to a final density of 1.0 x 10⁶ cells/mL. Mix thoroughly.
      NOTE: RPM1640 with 10% FBS, 100 U/mL penicillin and 100 µg/mL streptomycin is used for NCI-H460. Use DMEM with 10% FBS, 100 U/mL penicillin and 100 µg/mL streptomycin for HepG2.
   3. Remove the humidity chamber from incubator. Use tweezers to carefully place the assembled 3D microcryogel array chip from step 3.1.9 in the humidity chamber. Take caution not to wet the microcryogels with water in the chamber.
   4. Mix the cell suspension thoroughly, then aliquot 3 µL of cell suspension directly onto the microcryogel into each well.
      NOTE: The pipette tip should lightly touch the surface of the microcryogel before expelling cell suspension. Cells are auto-loaded into the microcryogel by absorption. Do not seed cells in the peripheral wells.
   5. Add 10 μL of media to each well after cells are seeded into microcryogel using multi-channel pipette, such as a 96-channel liquid handler. Medium is also added to peripheral wells.
      NOTE: Use RPM1640 media with 10% FBS, 100 U/mL penicillin and 100 µg/mL streptomycin for H460 cells. Use DMEM media with 10% FBS, 100 U/mL penicillin and 100 µg/mL streptomycin for HepaG2 cells.
   6. Culture the cell-loaded microcryogel array chip in the humidity chamber for 24 h in a humidified 5% CO₂ incubator at 37 °C to form 3D microtissue array.
   7. Dissolve doxorubicin and IMMLG-8439⁹ in dimethyl sulfoxide (DMSO) to form a stock solution of 10 mM. Dilute drugs with culture medium to form a 10-fold dilution concentration gradient from 2 nM to 200 µM.
   8. Add 10 µL of drug solutions into each well. Use 0.1% DMSO (diluted in medium) as the control. Incubate the drug loaded 3D microtissue array in a humidified 5% CO₂ incubator at 37 °C for 24 h.
   9. Add 4 µL of resazurin stock solution to each well. Incubate at 37 °C for 2 h. Place the 3D microtissue array in the microplate reader and detect fluorescence of resazurin metabolized by viable cells at an excitation light wavelength of 560 nm and emission light wavelength of 590 nm.
   10. Subtract the resazurin baseline signal from all wells before further data processing. Calculate the cell viability fraction of each well by dividing its fluorescence signal by the average fluorescence signal of the control wells.
   11. Plot the dose-response curve in plotting software with the cell viability fraction as the Y-axis and the base 10 logarithm of drug concentration as the X-axis. Interpolate the 50% inhibition concentration (IC50) at the cell viability fraction of 0.5.

Results

Fabrication and characterization of microcryogels for 3D microtissue formation.

According to this protocol, microcryogels were fabricated to form the 3D microtissues and individual microcryogels or microcryogel arrays, and were applied to regenerative therapy and drug screening, respectively (Figure 1). Microstencil array chips fabricated from PMMA were applied as micromolds for mic...

Discussion

Regenerative medicine and in vitro models for drug screening are two important applications for tissue engineering^5,6,7,8,9. While these two applications have vastly different needs, a common ground between them lies in the need for a more biomimetic culturing condition to enhance cell functions¹⁹. Only with improved cell funct...

Materials

List of materials used in this article

Name	Company	Catalog Number	Comments
Gelatin	sigma	G7041	All other reagents were purchased from Sigma-Aldrich (St. Louis, MO) unless otherwise indicated.
Glutaraldehyde	J&K	902042	Used as crosslinker in preparation of material.
Glass cover slip (24 x 50 mm)	CITOGLASS, China	10212450C	To scrape prcursor solution onto microstencils array chips.
Sodium borohydride, NaBH4	Beijing Chemical Works	116-8	To wash remaining glutaraldehyde away after gelation.
Vacuum jar	asperts, China	VC8130	To preserve microgels under vacuum.
Polymethylmethacrylate (PMMA) sheets	Sunjin Electronics Co., Ltd, China		Ordinary PMMA sheets.
Rayjet laser system	Rayjet, Australia	Rayjet 50 C30	To engrave PMMA sheets to form wells.
Plasma Cleaner	Mycro Technologies, USA	PDC-32G	To make PMMA hyphophilic.
Lyophilizer	Boyikang, China	SC21CL	To lyophilize materials.
Trypan Blue solution (0.4%)	Zhongkekeao, China	DA0065	To dye microgels.
Doxorubicin hydrochloride	ENERGY CHEMICAL, China	A01E0801360010	To test drug resistance of cells in 2D or 3D microgel.
Live/dead assay	Dojindo Molecular Technologies (Kumamoto, Japan)	CS01-10	To distinguish alive and dead cells.
Cell Titer-Blue	Promega (Wisconsin, USA).	G8080	To test cell viability.
Cell strainer	BD Biosciences, USA	352360	To collect microgels.
D-Luciferin	SYNCHEM (Germany)	s039	To tack cells.
Scanning electron microscope	FEI, USA	Quanta 200	To characterize microgel morphology.
Mechanical testing machine	Bose, USA	3230	To measure mechanical features.
Programmable syringe pump	World Precision Instruments, USA	ALADINI 1000	To test injactabiliy.
Digital force gauge	HBO, Yueqing Haibao Instrument Co., Ltd., China	H-50	To test injactabiliy.
Ethylene oxide sterilization system	Anprolene, Anderson Sterilization, Inc., Haw River, NC	AN74i	To sterilize microgels with ethylene oxide gas.
Microplate reader	Molecular Devices,USA	M5	To measure fluorescence intensity in micro-array.
Confocal microscope	Nikon, Japan	A1Rsi	To observe cell distribution in 3D.
Xenogen  Lumina II imaging system	Caliper Life Sciences, USA	IVIS	To track cell in animals.
Liquid work stataion	Apricot design,USA	S-pipette	To load medium or cell suspension high-throuputly.