This study was supported by a grant from JSPS KAKENHI (Grant No. 23390072 and 19K07335) and AMED (Grant No. A-149).

The animal experiments were conducted according to the Kansai-Medical University ethical guidelines for animal experiments and were approved by the ethical committees (approval number: 23-104). All the animals were raised under a constant light-dark cycle in a specific pathogen-free environment. All the sterilized surgical tools, such as scissors, forceps, and retractors, were autoclaved and dried thoroughly.
1. Preparation of the neonatal rat cardiomyocyte balls
<ol>
	<li>Neonatal rat heart collection
	<ol>
		<li>For the heart collection, follow a procedure similar to that described in a previous report7.</li>
		<li>Immerse neonatal (0-2 days after birth) Sprague-Dawley (SD) rats in povidone-iodine and 70% ethanol solutions sequentially, and then transfer them into an air-tight case filled with vaporized isoflurane (the concentration should be over 10% v/v) for deep anesthesia.</li>
		<li>After the confirmation of unconsciousness by a loss of locomotor activity, decapitate the ratwhile holding the body from the back with the hand, and then cut 2-4 mm of tissue from the frontal center of the ribcage to the caudal and then in the rostral direction using sharp scissors.</li>
		<li>Grip the back skin to pull the cut open and push out the heart from the ribcage. Cut the ventricles using scissors and immerse them in phosphate-buffered saline (PBS) without calcium or magnesium (PBS(&#8722;)).</li>
	</ol>
	</li>
	<li>Dispersion of the neonatal rat cardiomyocytes
	<ol>
		<li>Mince the collected ventricles dispersed in a minimal amount of Ads buffer (Ads buffer: 116 mM NaCl, 20 mM HEPES, 12.5 mM NaH2PO4, 5.6 mM glucose, 5.4 mM KCl, 0.8 mM MgSO4, pH 7.35) in an autoclaved concave glassware into small pieces (1 mm x 1 mm) using curved scissors.</li>
		<li>Transfer the minced tissues and a micro-magnetic stirrer into a 50 mL centrifugation tube, and disperse the tissues into single cells with 0.1% collagenase, 0.1% trypsin, 20 &#181;g/mL DNase I, and 50 nM tetramethylrhodamine methyl ester in Ads buffer at 37 &#176;C by stirring for 30 min.</li>
		<li>Separate the aggregates and dispersed cells through natural sedimentation, collect only the dispersed cells into a tube, and digest the residual cell aggregates again with the same digestion medium.</li>
		<li>Continue this procedure until all the cells are completely dissociated. To confirm the complete dispersion of the cells, observe the tubes under a microscope (4x objective lens).</li>
		<li>Collect the dispersed cells using centrifugation at 150 x g for 5 min and dissociate them in 1-2 mL of Ads buffer.</li>
	</ol>
	</li>
	<li>Fluorescence-activated cell sorting of cardiomyocytes
	<ol>
		<li>Analyze the cells using fluorescence-activated cell sorting (FACS) using 556-601 nm bandpass filters to detect red fluorescence signals.</li>
		<li>Carefully perform pre-gating to eliminate doublet fractions14. The gate settings for doublet elimination should be as per the manufacturer&#39;s instructions.</li>
		<li>Set the forward scatter on the x-axis and the red fluorescence signal on the y-axis. Three populations were observed: a lowermost population containing erythrocytes and dead cells, a middle population containing non-cardiomyocytes, including fibroblasts and endothelial cells, and a top population containing pure ventricular cardiomyocytes7.</li>
	</ol>
	</li>
	<li>Preparation of red fluorescence-labeled cardiomyocyte balls
	<ol>
		<li>Selectively sort the cardiomyocytes, and centrifuge for 5 min at 150 x g. Completely dissolve the cell pellets in 1 mL of alpha-modified minimal essential medium (alpha-MEM) containing 10% heat-inactivated fetal bovine serum (FBS).</li>
		<li>Measure the cell concentration using a hemocytometer and dilute the cell suspension solution to 3,000 cells/mL with alpha-MEM 10% FBS.</li>
		<li>Distribute them into cell non-adhesive 96-well plates (100 &#181;L per well), centrifuge for 5 min at 100 x g, and culture for 2-3 d in a cell culture incubator with 5% CO2 at 37 &#176;C.</li>
		<li>Before the injection experiments, harvest a cardiomyocyte ball from each well via aspiration with the culture medium using a 1,000 &#181;L pipette, and collect them in a 15 mL tube.</li>
		<li>Stain with PKH26 following the manufacturer&#39;s instructions for tracking after engraftment.</li>
	</ol>
	</li>
</ol>
2. Preparations for the slow injection method
<ol>
	<li>Preparation of the gelatin stock solution
	<ol>
		<li>Weigh the gelatin, dissolve it in Ads buffer to produce a 10% w/v solution, and autoclave it.</li>
	</ol>
	</li>
	<li>Production of a cell injection device
	<ol>
		<li>Overall device design: Prepare the apparatus shown in Figure 1. This system is combined with a syringe cooling apparatus and main injection apparatus.</li>
		<li>Prepare the main injection apparatus described below:
		<ol>
			<li>For a neonatal cardiomyocyte ball injection, use a 29 G, 50 mm long needle equipped with a syringe.</li>
			<li>Connect a power transfer syringe (18G, 1 mL) back-to-back using a cell injection syringe (Figure 1). Connect the needle of the power transfer syringe to a thin polypropylene tube with low lumen expandability.</li>
			<li>Then, connect the other side of the power transfer tube to the needle of the same syringe (18G, 1 mL), and set it in a syringe pump. Fill the two power transfer syringes and tubes with water without any air bubbles. 
			NOTE: When one plunger of the power transfer syringe is pushed in, the pressure is directly transferred to the other syringe, and the plunger protrudes.</li>
		</ol>
		</li>
		<li>Set up the injection syringe cooling system as described below.
		<ol>
			<li>Wind a copper tube (external diameter = 1 mm; internal diameter = 0.3 mm; thickness = 0.35 mm) tightly around the cell-containing part of the cell injection syringe, leaving 10 mm of excess pipe at both ends.</li>
			<li>Connect the copper tube to flexible plastic tubing. Further, connect the other ends of the plastic tubing to an external pump, fill the line with cooling water, and cool the water by immersing the excess copper tube into crushed ice (Figure 1). 
			NOTE: This cooling system maintains the cell suspension solution in the cylinder at approximately 2 &#176;C.</li>
		</ol>
		</li>
	</ol>
	</li>
</ol>
3. Development of a rat myocardial infarction model by obtuse coronary artery occlusion
<ol>
	<li>Anesthetize male immune-deficient nude rats (F344/Njcl-rnu/rnu) with air containing 3% isoflurane. Insert a cannula into the trachea and connect it to the respirator.</li>
	<li>Connect a cannula to an isoflurane vaporizer with a controller to maintain an 3% isoflurane concentration and, thus, sustain sufficient anesthesia. Confirm no response to pain stimuli. Apply veterinarian ointment on the eyes to prevent dryness.</li>
	<li>Fix the limbs with cut surgical tapes on a 40 &#176;C warmed surgical plate. Twist the body of the rat to the right of the body axis and use the left armpit as the surgical field.</li>
	<li>Remove the hair in the surgical field using a depilatory cream and wipe the skin with povidone-iodine. Using sharp scissors, cut a 1.5 cm incision in the skin and pectoralis major muscle.</li>
	<li>Confirm the third intercostal space and rip the intercostal muscles and costal pleura using micro forceps with blunt tips. Keep the chest open by using a retractor. Gently remove the thin pericardium with forceps.</li>
	<li>To construct an infarction model of the lateral wall of the heart, find the position 1 mm caudal to the tip of the left atrium to identify the obtuse coronary artery, pass a 7-0 silk suture, scoop up tissue that is 2.5 mm wide and 2.5 mm deep from dorsal to ventral, and ligate the tissue tightly.</li>
	<li>Confirm successful ligation by the weak contraction distal from the ligature. After gently removing the retractor, place a 5-0 silk suture between the second and fourth intercostal spaces, and close the thoracotomy.</li>
	<li>Decrease the isoflurane concentration to 1%. Gently suture the muscle and skin with 5-0 silk. Decrease the isoflurane concentration to 0% and wait for approximately 5 min until spontaneous breathing starts.</li>
	<li>Topically apply 2 mg/mL lidocaine in saline to the incision. Administrate 1 mL of saline via a subcutaneous injection. Apply veterinarian ointment topically to prevent infections.</li>
	<li>Remove the rat from the intubation tube, and return to the animal cage; then, raise the rats in individual cages for 1 week.</li>
	<li>Analyze the changes in the cardiac systolic pump function using echocardiography. 
	&#8203;NOTE: The cardiac function will be reduced owing to lateral myocardial infarction.</li>
</ol>
4. Echo-guided percutaneous cell transplantation using the slow injection method
<ol>
	<li>Pre-warm 10% gelatin stock at 37 &#176;C until it becomes liquid.</li>
	<li>Dilute 10% gelatin stock with pre-warmed Ads buffer to obtain the final injectable 5% w/v gelatin solution (100 &#181;L is required per animal).</li>
	<li>Suspend 96 cardiomyocyte balls (total: 28,800 cardiomyocytes/animal) in 100 &#181;L of pre-warmed injection solution.</li>
	<li>Load the suspension prepared in step 4.3 into the cell injection syringe, avoiding the aspiration of excess air.</li>
	<li>To eliminate bubbles in the syringe, hold it vertically with the needle upward, tap the syringe, and collect any bubbles at the upper ridge of the syringe. 
	NOTE: During this step, observe the cardiomyocyte balls gradually settle onto the rubber seal of the plunger.</li>
	<li>Maintain the vertical position of the syringe, push up the plunger slowly, and discard the bubbles and excess cell suspension solution until 20 &#181;L of the cell suspension remains in the syringe. Push the plunger carefully at a constant speed so that the cardiomyocyte ball remains resting on the rubber seal of the plunger.</li>
	<li>Immerse the capped syringe directly in an ice bath for 5 min.</li>
	<li>Place a cooled syringe in the injection apparatus. Tightly fix the injection syringe apparatus settled on a fine movement device on the animal stage using an X-Y-Z position-adjustable handmade clamp. The fine movement device can move the needle position using the x-direction 20 mm slide, y-direction swing, and z-direction bowing movements.</li>
	<li>Anesthetize the rats in a sealed box filled with air containing 3% isoflurane. Confirm anesthesia by no response to pain stimuli. Apply veterinarian ointment on the eyes to prevent dryness.</li>
	<li>Fix the limbs with cut surgical tapes on a 40 &#176;C warmed echo plate. To sustain sufficient anesthesia, ensure the inhaled air contains an approximately 3% concentration of isoflurane.</li>
	<li>Remove the hair at the injection field (2 cm in diameter) and chest with depilatory cream and wipe the skin with povidone-iodine.</li>
	<li>Apply echo-gel on the chest and echo probe. Place the echo probe close to the chest along the cranial and caudal axes and start to obtain B-mode echocardiography following the manufacturer&#39;s manual.</li>
	<li>Advance the tip of the injection needle into the myocardium at the frontal view (Figure 2 and Supplementary Video 1).</li>
	<li>To activate the main syringe pump, push the Start button, and rotate the dial to adjust to a predetermined number for an injection speed of approximately 0.02 &#181;L/s. Apply veterinarian ointment topically around the needling position to prevent infections. 
	NOTE: It is necessary to determine the appropriate dial number for the intended injection speed using an injection solution. After the injection, remove the injection needle using an exemplary movement system.</li>
	<li>Decrease the isoflurane concentration to 0% and wait for approximately 5 min until the animal regains sufficient consciousness to maintain sternal recumbency.</li>
</ol>
5. Evaluation of cardiac function
<ol>
	<li>Anesthetize the rats in a sealed box filled with air containing 3% isoflurane. Confirm anesthesia by no response to pain stimuli. Apply veterinarian ointment on the eyes to prevent dryness.</li>
	<li>Apply electrifying cream for ECG acquisition on the limb tips. Fix the limbs with cut surgical tapes on a 40 &#176;C warmed echo plate. Use a physiological monitoring system to detect real-time ECG and heart rate.</li>
	<li>According to the manufacturer&#39;s instructions, first determine the long-axis angle using the B-mode echo image showing the left ventricular apex to the outflow tract, and then rotate the echo-probe 90&#176; to change to the short-axis view.</li>
	<li>Using only the caudal to rostral axis fine movement system of the animal stage, adjust the short-axis view to the papillary muscle level. Then, change the image mode to M-mode by pressing the M-mode button, and record a video for 5 s by pressing the Cine-loop button.</li>
	<li>To analyze and calculate the fraction shortening using the software, press the Measure button and a vertical line tool to define the end-systolic and end-diastolic left ventricular internal dimensions. The software automatically calculates the percent fraction shortening (FS).</li>
	<li>Decrease the isoflurane concentration to 0% and wait for approximately 5 min until the animal regains sufficient consciousness to maintain sternal recumbency.</li>
</ol>
6. Immunohistochemistry
<ol>
	<li>Fix the euthanized body (perform euthanasia as in step 1.1.3) on the table using the cut surgical tapes, excise the hearts, wash with PBS, and immerse the heart in 4% paraformaldehyde/PBS.</li>
	<li>Dissect the hearts into three sections, immerse them in 40% sucrose for cryoprotection, embed in an optimal cutting temperature (OCT) compound, and freeze them at &#8722;80 &#176;C.</li>
	<li>Attach the cryosectioned tissues (8 &#181;m thickness) to aminosilane-coated glass slides. After sufficient drying using non-warmed wind generated by a general hair dryer, immerse the glass slides in tris-buffered saline containing 0.2% Tween-20 (TBS-T).</li>
	<li>Immerse them in a blocking solution for 30 min at 25 &#176;C. Pour 100 &#181;L of the primary antibody-containing blocking solution onto the slide, and incubate overnight at 4 &#176;C with paraffin sealing to keep the antibody solution spread on the tissue. 
	NOTE: The antibody concentration is shown in the Table of Materials.</li>
	<li>Lay the slides horizontally in a handmade high-humidity box utilizing the natural vapor from wet paper to prevent evaporation. Wash the slides three times with TBS-T.</li>
	<li>Treat with the secondary antibody-containing blocking agent for 1 h at 25 &#176;C in the same manner as the primary antibody. After three washes, observe the fluorescence signals using a fluorescence microscope and confocal laser microscope. 
	NOTE: The antibody concentration is shown in the Table of Materials.</li>
	<li>Statistical analysis: For the cell volume comparison, as shown in Figure 3A, perform a non-paired t-test; to assess the cardiac functional recovery following cardiomyocyte administration using the slow injection method, as shown in Figure 4A, use a paired t-test. In this work, differences were considered statistically significant at P &#60; .01. Error bars represent the standard deviation.</li>
</ol>

A Novel Minimally Invasive Slow Injection Method for Reducing Tissue Injury

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K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+role+of+monocytes+in+optic+nerve+injury.">The role of monocytes in optic nerve injury.</a> Neural Regeneration Research. 18 (8), 1666-1671 (2023).</li><li>Weber, F., Treeck, O., Mester, P., Buechler, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Expression+and+function+of+BMP+and+activin+membrane-bound+inhibitor+(BAMBI)+in+chronic+liver+diseases+and+hepatocellular+carcinoma.">Expression and function of BMP and activin membrane-bound inhibitor (BAMBI) in chronic liver diseases and hepatocellular carcinoma.</a> International Journal of Molecular Sciences. 24 (4), 3473 (2023).</li><li>Tohyama, S., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Distinct+metabolic+flow+enables+large-scale+purification+of+mouse+and+human+pluripotent+stem+cell-derived+cardiomyocytes.">Distinct metabolic flow enables large-scale purification of mouse and human pluripotent stem cell-derived cardiomyocytes.</a> Cell Stem Cell. 12 (1), 127-137 (2013).</li><li>Hattori, F., Fukuda, K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Strategies+for+replacing+myocytes+with+induced+pluripotent+stem+in+clinical+protocols.">Strategies for replacing myocytes with induced pluripotent stem in clinical protocols.</a> Transplantation Reviews. 26 (3), 223-232 (2012).</li><li>Hattori, F., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nongenetic+method+for+purifying+stem+cell-derived+cardiomyocytes.">Nongenetic method for purifying stem cell-derived cardiomyocytes.</a> Nature Methods. 7 (1), 61-66 (2010).</li><li>Fernandes, S., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Human+embryonic+stem+cell-derived+cardiomyocytes+engraft+but+do+not+alter+cardiac+remodeling+after+chronic+infarction+in+rats.">Human embryonic stem cell-derived cardiomyocytes engraft but do not alter cardiac remodeling after chronic infarction in rats.</a> Journal of Molecular and Cellular Cardiology. 49 (6), 941-949 (2010).</li><li>Shiba, Y., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Allogeneic+transplantation+of+iPS+cell-derived+cardiomyocytes+regenerates+primate+hearts.">Allogeneic transplantation of iPS cell-derived cardiomyocytes regenerates primate hearts.</a> Nature. 538 (7625), 388-391 (2016).</li><li>Wendel, J. 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The author has nothing to disclose.

One of the critical points in the successful performance of the slow injection method is the preparation of an effective injection system using a powerful syringe pump and a strong pressure transfer tube. A high-pressure system is required to push gel out from the tip of a fine needle. The second critical point is the stabilization of the heart. The beating of the heart against an injection needle advanced into the myocardium can injure the tissue. In this study, an echo-guided injection was conducted to avoid the animals undergoing a second open chest injury and to administer the cell injection in a stabilized heart with the lungs inflated. Moreover, in some applications for larger animals or humans, some injection devices attached onto the heart should be considered as part of the strategic design of the application. For open chest injections into the hearts of small animals, the use of a long, flexible needle is recommended given their higher heart rates.
In this work, the slow injection method significantly increased the surviving cardiomyocyte volume compared to the normal injection method. The normal injection causes cell damage via shear stress15. In contrast, the slow injection method does not cause such stress theoretically because it uses a non-Newtonian solution in addition to the slow injection.
In terms of local fibrosis, the interstitial space around the normally injected surviving cardiomyocytes showed strong and widespread type I collagen deposition. In contrast, the type I collagen signals around the engrafted cardiomyocytes grafted using the slow injection method were much weaker and more limited. This suggests that the slow injection method caused significantly less damage. The slow injection of neonatal cardiomyocytes into the adult myocardium significantly improved the contractile function of the infarcted heart. The histological analyses suggested that grafting the cardiomyocytes using the slow injection method resulted in direct connections and functional coupling with the host cardiomyocytes. This phenomenon explains the mechanism of the functional recovery of the host myocardium. To the best of our knowledge, this is the first report of engrafted neonatal cardiomyocytes with large-scale seamless connections to the host adult cardiomyocytes. The functional connections with the host myocardium via electrical and mechanical coupling may make the engrafted cardiomyocytes mature and allow them to act as functional myocytes that contribute to the host heart function. Long-term physical force interactions between the host and graft cardiomyocytes are crucial for full maturation. Therefore, 2 months might be required after the injection for the functional recovery of the infarcted heart. The time-dependent recovery of the patient&#39;s heart function may be an expected phenomenon in therapeutic applications, and this can be a hallmark of the successful establishment of de novo functional coupling and integration between the host and grafted cardiomyocytes.
The slow injection method can be performed during open chest surgery. In addition, this method can be applied to mice. For future applications in human therapy, we still need to resolve several issues. The injection speed should be optimized by considering the buffer capacity of the interstitial fluid flow in each human target organ. Xeno-free materials, such as human gelatin or biodegradable synthetic materials, should be applied. Clinical GMP-grade slow injection apparatus, such as compact organ-specific disposable tools or a reusable wide-organ applicable apparatus, should be developed.

Cell administration and replacement are promising novel therapeutic strategies for heavily damaged organs. Among these novel therapeutic strategies, cardiac regenerative medicine has attracted considerable attention. However, the inflammation caused by injuries mediates scar formation in several organs1,2,3,4. The human heart consists of approximately 1010 cardiomyocytes; therefore, theoretically5,6, it must be treated with more than 109 cardiomyocytes. Administering a large number of cardiomyocytes via traditional injection methods may lead to significant tissue injuries7. This method provides a novel cell injection method with minimal tissue invasion.
Cell administration into the organ parenchyma requires injection(s). However, a discrepancy exists in that the injection itself may lead to tissue injury. Tissue injury causes local inflammation and incurable scarring in organs and tissues, as well as impaired regenerative ability8,9,10. The mammalian heart has an extremely high propensity to develop scars instead of regenerating because it requires immediate injury repair in order to endure the high blood pressure caused by its continuous pumping function11. Ablation therapy utilizes this high propensity toward scar formation and blocks the circuit likely to undergo scar formation using arrhythmia12. In a previous study, it was observed that the scar tissue isolated the injected cardiomyocytes in the host myocardium. Thus, this represents the next target issue that needs to be overcome to obtain improved therapeutic efficacy in cardiac regenerative medicine.
Tissue interstitial fluid flow plays a vital role in conveying oxygen and nutrients to cells and removing the excreted waste from cells. The physiological speed of interstitial fluid flow in each tissue/organ is different (the range is 0.01-10 &#181;m/s)13. To the best of the author&#39;s knowledge, there are no data regarding the capacity of individual tissues/organs to support extra amounts of fluid without pathological edema; however, this experiment attempts to use a slow injection speed to possibly reduce tissue injury, and the results can be used to determine the practicality of this concept.

<table border="1" fo:keep-together.within-page="1" fo:keep-with-next.within-page="always">
	<tbody>
		<tr>
			<td>18-gauge needle &#38; tuberculin, 1 mL</td>
			<td>Terumo&#160;</td>
			<td>NN1838R, SS-01T</td>
			<td></td>
		</tr>
		<tr>
			<td>29-gauge 50 mm-long needle</td>
			<td>Ito Corporation, Tokyo, Japan</td>
			<td>14903 Type-A&#160;</td>
			<td></td>
		</tr>
		<tr>
			<td>A copper tube</td>
			<td>General Suppliers</td>
			<td></td>
			<td>outer diameter, 1 mm; inner diameter, 0.3 mm; thickness, 0.35 mm</td>
		</tr>
		<tr>
			<td>Ads Buffer</td>
			<td>Each ingredient was purchased from Fuji Film Wako Chemical Inc., Miyazaki, Japan</td>
			<td></td>
			<td>Hand made, Composition: 116 mM NaCl, 20 mM HEPES, 12.5 mM NaH2PO4, 5.6 mM glucose, 5.4 mM KCl, 0.8 mM MgSO4, pH 7.35</td>
		</tr>
		<tr>
			<td>alpha-MEM</td>
			<td>Fuji Film Wako Chemical Inc., Miyazaki, Japan</td>
			<td>051-07615</td>
			<td></td>
		</tr>
		<tr>
			<td>Anti-collagen type I rabbit polyclonal antibody (H+L)</td>
			<td>Proteintech</td>
			<td>14695-1-AP</td>
			<td>using dilution 1:100</td>
		</tr>
		<tr>
			<td>Anti-Connexin-43 rabbit polyclonal antibody (H+L)</td>
			<td>Sigma Aldrich</td>
			<td>C6219</td>
			<td>using dilution 1:100</td>
		</tr>
		<tr>
			<td>Anti-rabbit IgG (H+L) donley polyclonal antibody-AlexaFluo488&#160;</td>
			<td>Thermo Scientific</td>
			<td>A21206</td>
			<td>using dilution 1:300</td>
		</tr>
		<tr>
			<td>blocking solution (Blocking One)</td>
			<td>Nacalai Tesque, Kyoto, Japan</td>
			<td>03953-95&#160;</td>
			<td></td>
		</tr>
		<tr>
			<td>collagenase</td>
			<td>Fuji Film Wako Chemical Inc., Miyazaki, Japan</td>
			<td>034-22363</td>
			<td></td>
		</tr>
		<tr>
			<td>confocal laser microscope</td>
			<td>Carl Zeiss Inc., Oberkochen, Germany</td>
			<td>LSM510 META</td>
			<td></td>
		</tr>
		<tr>
			<td>DNase I</td>
			<td>Sigma-Aldrich</td>
			<td>DN25</td>
			<td></td>
		</tr>
		<tr>
			<td>FACS Aria III</td>
			<td>Becton Dickinson, Franklin Lakes, NJ, USA</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>fetal bovine serum</td>
			<td>BioWest, FL, USA</td>
			<td>S1820-500</td>
			<td></td>
		</tr>
		<tr>
			<td>fine movement device (Micromanipulator)</td>
			<td>Narishige Co., Ltd., Tokyo, Japan</td>
			<td>M-44</td>
			<td></td>
		</tr>
		<tr>
			<td>fluorescence microscope</td>
			<td>&#160;Nikon Instruments, Tokyo, Japan</td>
			<td>Eclipse Ti2</td>
			<td></td>
		</tr>
		<tr>
			<td>gelatin from bovine skin</td>
			<td>Sigma-Aldrich</td>
			<td>G9382</td>
			<td>dissolving in PBS (-) to 10%, and autoclaving it</td>
		</tr>
		<tr>
			<td>Neonatal Sprague-Dawley (SD) rats</td>
			<td>Japan SLC Inc., Shizuoka, Japan</td>
			<td></td>
			<td>0&#8211;2 d after birth</td>
		</tr>
		<tr>
			<td>non-adhesive 96-well plates (spheloid plate)</td>
			<td>Sumitomo Bakelite, Tokyo, Japan</td>
			<td>MS-0096S</td>
			<td></td>
		</tr>
		<tr>
			<td>Optimal Cutting Temperature (OCT) Compound&#160;</td>
			<td>Sakura Finetek USA, Inc., CA, USA</td>
			<td>Tissue-Tek OCT compound</td>
			<td></td>
		</tr>
		<tr>
			<td>peristaltic pump (for cooling system)</td>
			<td>As One Co., Osaka, Japan</td>
			<td>SMP-23AS</td>
			<td></td>
		</tr>
		<tr>
			<td>PKH26</td>
			<td>Sigma-Aldrich</td>
			<td>PKH26GL</td>
			<td></td>
		</tr>
		<tr>
			<td>Stir Bar, Micro, Magnetic, PTFE, Length x Dia. in mm: 5 x 2</td>
			<td>Chemglass life sciences LLC, NJ, USA</td>
			<td>CG-2003-120</td>
			<td></td>
		</tr>
		<tr>
			<td>syringe&#160;</td>
			<td>Ito Corporation, Tokyo, Japan</td>
			<td>MS-N25</td>
			<td></td>
		</tr>
		<tr>
			<td>syringe pump with remote controller</td>
			<td>As One Co., Osaka, Japan</td>
			<td>MR-1, CT-10</td>
			<td></td>
		</tr>
		<tr>
			<td>tetramethylrhodamine methyl ester</td>
			<td>Thermo Fisher Scientific, Waltham, MA, USA</td>
			<td>T668</td>
			<td></td>
		</tr>
		<tr>
			<td>trypsin</td>
			<td>DIFCO, Becton Dickinson, Franklin Lakes, NJ, USA</td>
			<td>215240</td>
			<td></td>
		</tr>
		<tr>
			<td>Tween-20</td>
			<td>Fuji Film Wako Chemical Inc., Miyazaki, Japan</td>
			<td>167-11515</td>
			<td></td>
		</tr>
		<tr>
			<td>veterinarian ointment</td>
			<td>&#160;Fujita Pharmaceutical Co., Ltd.</td>
			<td>Hibikusu ointment&#160; #WAK-95832</td>
			<td></td>
		</tr>
		<tr>
			<td>Vevo 2100 Imaging System</td>
			<td>Fujifilm VisualSonics, Inc., Toronto, Canada</td>
			<td>Vevo 2100</td>
			<td></td>
		</tr>
		<tr>
			<td>Vevo 2100 Imaging System software version 1.0.0</td>
			<td>Fujifilm VisualSonics, Inc., Toronto, Canada</td>
			<td>Vevo 2100</td>
			<td></td>
		</tr>
		<tr>
			<td>Weakly curved needle with ophthalmic thread</td>
			<td>Natsume Seisakusho Co., Ltd., Tokyo, Japan</td>
			<td>C7-70</td>
			<td></td>
		</tr>
	</tbody>
</table>

a novel cell injection method with minimum invasion

Directly injecting cells into tissues is a necessary process in cell administration and/or replacement therapy. The cell injection requires a sufficient amount of suspension solution to allow the cells to enter the tissue. The volume of the suspension solution affects the tissue, and this can cause major invasive injury as a result of the cell injection. This paper reports on a novel cell injection method, called slow injection, that aims to avoid this injury. However, pushing out the cells from the needle tip requires a sufficiently high injection speed according to Newton's law of shear force. To solve the above contradiction, a non-Newtonian fluid, such as gelatin solution, was used as the cell suspension solution in this work. Gelatins solution have temperature sensitivity, as their form changes from gel to sol at approximately 20 &#176;C. Therefore, to maintain the cell suspension solution in the gel form, the syringe was kept cooled in this protocol; however, once the solution was injected into the body, the body temperature converted it to a sol. The interstitial tissue fluid flow can absorb excess solution. In this work, the slow injection technique allowed cardiomyocyte balls to enter the host myocardium and engraft without surrounding fibrosis. This study employed a slow injection method to inject purified and ball-formed neonatal rat cardiomyocytes into a remote area of myocardial infarction in the adult rat heart. At 2 months following the injection, the hearts of the transplanted groups showed significantly improved contractile function. Furthermore, histological analyses of the slow-injected hearts revealed seamless connections between the host and graft cardiomyocytes via intercalated disks containing gap junction connections. This method could contribute to next-generation cell therapies, particularly in cardiac regenerative medicine.

Effects of the slow injection on cell survival and collagen deposition 
Neonatal rat cardiomyocyte balls labeled with PKH26 were injected into normal nude rat myocardium using a normal or slow injection method. The results showed that the slow injection method significantly increased the engrafted cell volume (Figure 3A) and significantly decreased on-site type I collagen deposition (Figure 3B).
Effects of slow injection on treatment efficacy in a rat infarction model 
The echocardiograph-guided slow injection method was used to inject neonatal rat cardiomyocyte balls or PBS(&#8722;) into the infarcted hearts of model rats. The cell-injected group alone exhibited significant improvement in heart contraction function after 2 months (Figure 4A). Immunohistochemical analyses revealed a seamless connection between the engrafted cells and host myocytes via intercalated disks containing gap junctions (Figure 4B).
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/65260/65260fig01.jpg" /> 
Figure 1: Schematic of the whole injection system. (A) Main injection apparatus. (B) Injection syringe cooling system. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/65260/65260fig01large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/65260/65260fig02.jpg" /> 
Figure 2: Echocardiography-guided percutaneous slow injection. (A) Setting of the animal, echo probe, and injection apparatus. (B) Echocardiographic view of the injecting syringe and heart. Note that the left and the right pictures are the same, but a yellow line has been added to indicate the needle position. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/65260/65260fig02large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/65260/65260fig03.jpg" /> 
Figure 3: Effect of the slow injection method on the engrafted cell volume and collagen deposition. (A) The engrafted cell volumes (N = 3) were calculated from serial sections. The error bars indicate standard deviations. *P &#60; 0.01 in a non-paired t-test. (B) Immunohistochemical staining for type I collagen. The scale bar indicates 200 &#181;m. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/65260/65260fig03large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/65260/65260fig04.jpg" /> 
Figure 4: Improvements in heart function and histological integration with cardiomyocyte balls engrafted by the slow injection method. (A) Representative echocardiograph M-mode views. The graph shows the transition of fraction shortenings in the cardiomyocyte ball-transplanted group (solid red line; N = 4) and vehicle (cell suspension solution for the slow injection method) group (dotted blue line; N = 3). Abbreviations: MI = myocardial infarction; Cx43 = connexin 43; DAPI = 4&#39;,6-diamidino-2-phenylindole; PKH26 = red fluorescent cell membrane label. The error bars indicate the standard deviations. *P &#60; 0.01 in a paired t-test. (B) Immunohistochemical analyses of the relationship between the engrafted cardiomyocyte balls and host cardiomyocytes. The conventional laser microscopic observations using a 2x objective lens are shown in the left column. Zoomed-in versions (using a 20x objective lens) of two areas shown in the box, labeled with * and #, are presented below. Scale bars: top image = 300 &#181;m; * and # = 30 &#181;m. Confocal laser microscopic images using a 20x objective lens are shown along for comaparison. Three positions are shown. In the merged images, the arrowheads indicate the existence of gap junctions (Cx43) directly connecting the graft and host cardiomyocytes. The scale bar indicates 30 &#181;m. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/65260/65260fig04large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
Supplementary Video 1: Echo-guided slow injection method. The B-mode echocardiogram in the frontal view shows the injection needle tip advanced into the myocardium. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/65260/Supplementary video.mp4" target="_blank">Please click here to download this File.</a>

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Author Spotlight: A Novel Cell Injection Method with Minimum Invasion  

This method eliminates any major invasion during cell injections caused by the cell suspension solution.

A Novel Cell Injection Method with Minimum Invasion

Directly injecting cells into tissues is a necessary process in cell administration and/or replacement therapy. The cell injection requires a sufficient ...

a-novel-cell-injection-method-with-minimum-invasion

Nanyang Technological University

Research

JoVE Journal

Bioengineering

1.3K Views.  Kansai Medical University. This method eliminates any major invasion during cell injections caused by the cell suspension solution.

Video: Author Spotlight: A Novel Cell Injection Method with Minimum Invasion  

Gold Nanostar Synthesis with a Silver Seed Mediated Growth Method

The physical, chemical and optical properties of nano-scale colloids depend on their material composition, size and shape 1-5. There is a great interest in using nano-colloids for photo-thermal ablation, drug delivery and many other biomedical applications 6. Gold is particularly used because of its low toxicity 7-9. A property of metal nano-colloids is that they can have a strong surface plasmon resonance 10. The peak of the surface plasmon resonance mode depends on the structure and composition of the metal nano-colloids. Since the surface plasmon resonance mode is stimulated with light there is a need to have the peak absorbance in the near infrared where biological tissue transmissivity is maximal 11, 12.
We present a method to synthesize star shaped colloidal gold, also known as star shaped nanoparticles 13-15 or nanostars 16. This method is based on a solution containing silver seeds that are used as the nucleating agent for anisotropic growth of gold colloids 17-22. Scanning electron microscopy (SEM) analysis of the resulting gold colloid showed that 70 % of the nanostructures were nanostars. The other 30 % of the particles were amorphous clusters of decahedra and rhomboids. The absorbance peak of the nanostars was detected to be in the near infrared (840 nm). Thus, our method produces gold nanostars suitable for biomedical applications, particularly for photo-thermal ablation.

We synthesized star shaped gold nanostars using a silver seed mediated growth method. The diameter of the nanostars ranges from 200 to 300 nm and the number of tips vary from 7 to 10. The nanoparticles have a broad surface plasmon resonance mode centered in the near infrared.

The physical, chemical and optical properties of nano-scale colloids depend on their material composition, size and shape 1-5. There is a great interest ...

Three-dimensional Cell Culture Model for Measuring the Effects of Interstitial Fluid Flow on Tumor Cell Invasion

The growth and progression of most solid tumors depend on the initial transformation of the cancer cells and their response to stroma-associated signaling in the tumor microenvironment 1. Previously, research on the tumor microenvironment has focused primarily on tumor-stromal interactions 1-2. However, the tumor microenvironment also includes a variety of biophysical forces, whose effects remain poorly understood. These forces are biomechanical consequences of tumor growth that lead to changes in gene expression, cell division, differentiation and invasion3. Matrix density 4, stiffness 5-6, and structure 6-7, interstitial fluid pressure 8, and interstitial fluid flow 8 are all altered during cancer progression.
Interstitial fluid flow in particular is higher in tumors compared to normal tissues 8-10. The estimated interstitial fluid flow velocities were measured and found to be in the range of 0.1-3 &mu;m s-1, depending on tumor size and differentiation 9, 11. This is due to elevated interstitial fluid pressure caused by tumor-induced angiogenesis and increased vascular permeability 12. Interstitial fluid flow has been shown to increase invasion of cancer cells 13-14, vascular fibroblasts and smooth muscle cells 15. This invasion may be due to autologous chemotactic gradients created around cells in 3-D 16 or increased matrix metalloproteinase (MMP) expression 15, chemokine secretion and cell adhesion molecule expression 17. However, the mechanism by which cells sense fluid flow is not well understood. In addition to altering tumor cell behavior, interstitial fluid flow modulates the activity of other cells in the tumor microenvironment. It is associated with (a) driving differentiation of fibroblasts into tumor-promoting myofibroblasts 18, (b) transporting of antigens and other soluble factors to lymph nodes 19, and (c) modulating lymphatic endothelial cell morphogenesis 20.
The technique presented here imposes interstitial fluid flow on cells in vitro and quantifies its effects on invasion (Figure 1). This method has been published in multiple studies to measure the effects of fluid flow on stromal and cancer cell invasion 13-15, 17. By changing the matrix composition, cell type, and cell concentration, this method can be applied to other diseases and physiological systems to study the effects of interstitial flow on cellular processes such as invasion, differentiation, proliferation, and gene expression.

Interstitial fluid flow is elevated in solid tumors and can modulate tumor cell invasion. Here we describe a technique to apply interstitial fluid flow to cells embedded in a matrix and then measure its effects on cell invasion. This technique can be easily adapted to study other systems.

The growth and progression of most solid tumors depend on the initial transformation of the cancer cells and their response to stroma-associated signaling ...

Tissue Engineering of Tumor Stromal Microenvironment with Application to Cancer Cell Invasion

3D organotypic cultures of epithelial cells on a matrix embedded with mesenchymal cells are widely used to study epithelial cell differentiation and invasion. Rat tail type I collagen and/or matrix derived from Engelbreth-Holm-Swarm mouse sarcoma cells have been traditionally employed as the substrates to model the matrix or stromal microenvironment into which mesenchymal cells (usually fibroblasts) are populated. Although experiments using such matrices are very informative, it can be argued that due to an overriding presence of a single protein (such as in type I Collagen) or a high content of basement membrane components and growth factors (such as in matrix derived from mouse sarcoma cells), these substrates do not best reflect the contribution to matrix composition made by the stromal cells themselves. To study native matrices produced by primary dermal fibroblasts isolated from patients with a tumor prone, genetic blistering disorder (recessive dystrophic epidermolysis bullosa), we have adapted an existing native matrix protocol to study tumor cell invasion. Fibroblasts are induced to produce their own matrix over a prolonged period in culture. This native matrix is then detached from the culture dish and epithelial cells are seeded onto it before the entire coculture is raised to the air-liquid interface. Cellular differentiation and/or invasion can then be assessed over time. This technique provides the ability to assess epithelial-mesenchymal cell interactions in a 3D setting without the need for a synthetic or foreign matrix with the only disadvantage being the prolonged period of time required to produce the native matrix. Here we describe the application of this technique to assess the ability of a single molecule expressed by fibroblasts, type VII collagen, to inhibit tumor cell invasion.

Tissue engineered fibroblast-derived native matrix is an emerging tool to generate a stromal substrate which supports epithelial cell proliferation and differentiation. Here a protocol applying this methodology to assess the impact of different stromal cell types on tumor cell biology is presented.

3D organotypic cultures of epithelial cells on a matrix embedded with mesenchymal cells are widely used to study epithelial cell differentiation and ...

A Novel Stretching Platform for Applications in Cell and Tissue Mechanobiology

Tools that allow the application of mechanical forces to cells and tissues or that can quantify the mechanical properties of biological tissues have contributed dramatically to the understanding of basic mechanobiology. These techniques have been extensively used to demonstrate how the onset and progression of various diseases are heavily influenced by mechanical cues. This article presents a multi-functional biaxial stretching (BAXS) platform that can either mechanically stimulate single cells or quantify the mechanical stiffness of tissues. The BAXS platform consists of four voice coil motors that can be controlled independently. Single cells can be cultured on a flexible substrate that can be attached to the motors allowing one to expose the cells to complex, dynamic, and spatially varying strain fields. Conversely, by incorporating a force load cell, one can also quantify the mechanical properties of primary tissues as they are exposed to deformation cycles. In both cases, a proper set of clamps must be designed and mounted to the BAXS platform motors in order to firmly hold the flexible substrate or the tissue of interest. The BAXS platform can be mounted on an inverted microscope to perform simultaneous transmitted light and/or fluorescence imaging to examine the structural or biochemical response of the sample during stretching experiments. This article provides experimental details of the design and usage of the BAXS platform and presents results for single cell and whole tissue studies. The BAXS platform was used to measure the deformation of nuclei in single mouse myoblast cells in response to substrate strain and to measure the stiffness of isolated mouse aortas. The BAXS platform is a versatile tool that can be combined with various optical microscopies in order to provide novel mechanobiological insights at the sub-cellular, cellular and whole tissue levels.

We present in this article a novel stretching platform that can be used to investigate single cell responses to complex anisotropic biaxial mechanical deformation and quantify the mechanical properties of biological tissues.

Tools that allow the application of mechanical forces to cells and tissues or that can quantify the mechanical properties of biological tissues have ...

Formation of Biomembrane Microarrays with a Squeegee-based Assembly Method

Lipid bilayer membranes form the plasma membranes of cells and define the boundaries of subcellular organelles. In nature, these membranes are heterogeneous mixtures of many types of lipids, contain membrane-bound proteins and are decorated with carbohydrates. In some experiments, it is desirable to decouple the biophysical or biochemical properties of the lipid bilayer from those of the natural membrane. Such cases call for the use of model systems such as giant vesicles, liposomes or supported lipid bilayers (SLBs). Arrays of SLBs are particularly attractive for sensing applications and mimicking cell-cell interactions. Here we describe a new method for forming SLB arrays. Submicron-diameter SiO2 beads are first coated with lipid bilayers to form spherical SLBs (SSLBs). The beads are then deposited into an array of micro-fabricated submicron-diameter microwells. The preparation technique uses a "squeegee" to clean the substrate surface, while leaving behind SSLBs that have settled into microwells. This method requires no chemical modification of the microwell substrate, nor any particular targeting ligands on the SSLB. Microwells are occupied by single beads because the well diameter is tuned to be just larger than the bead diameter. Typically, more 75% of the wells are occupied, while the rest remain empty. In buffer SSLB arrays display long-term stability of greater than one week. Multiple types of SSLBs can be placed in a single array by serial deposition, and the arrays can be used for sensing, which we demonstrate by characterizing the interaction of cholera toxin with ganglioside GM1. We also show that phospholipid vesicles without the bead supports and biomembranes from cellular sources can be arrayed with the same method and cell-specific membrane lipids can be identified.

Supported lipid bilayers and natural membrane particles are convenient systems that can approximate the properties of cell membranes and be incorporated in a variety of analytical strategies. Here we demonstrate a method for preparing microarrays composed of supported lipid bilayer-coated SiO2 beads, phospholipid vesicles or natural membrane particles.

Lipid bilayer membranes form the plasma membranes of cells and define the boundaries of subcellular organelles. In nature, these membranes are ...

A Novel Method for Localizing Reporter Fluorescent Beads Near the Cell Culture Surface for Traction Force Microscopy

PA gels have long been used as a platform to study cell traction forces due to ease of fabrication and the ability to tune their elastic properties. When the substrate is coated with an extracellular matrix protein, cells adhere to the gel and apply forces, causing the gel to deform. The deformation depends on the cell traction and the elastic properties of the gel. If the deformation field of the surface is known, surface traction can be calculated using elasticity theory. Gel deformation is commonly measured by embedding fluorescent marker beads uniformly into the gel. The probes displace as the gel deforms. The probes near the surface of the gel are tracked. The displacements reported by these probes are considered as surface displacements. Their depths from the surface are ignored. This assumption introduces error in traction force evaluations. For precise measurement of cell forces, it is critical for the location of the beads to be known. We have developed a technique that utilizes simple chemistry to confine fluorescent marker beads, 0.1 and 1 &#181;m in diameter, in PA gels, within 1.6 &#956;m of the surface. We coat a coverslip with poly-D-lysine (PDL) and fluorescent beads. PA gel solution is then sandwiched between the coverslip and an adherent surface. The fluorescent beads transfer to the gel solution during curing. After polymerization, the PA gel contains fluorescent beads on a plane close to the gel surface.

Traditional techniques for fabricating polyacrylamide (PA) gels containing fluorescent probes involve sandwiching a gel between an adherent surface and a glass slide. Here, we show that coating this slide with poly-D-lysine (PDL) and fluorescent probes localizes the probes to within 1.6 &#181;m from the gel surface.

PA gels have long been used as a platform to study cell traction forces due to ease of fabrication and the ability to tune their elastic properties. When ...

Rapid Subtractive Patterning of Live Cell Layers with a Microfluidic Probe

The microfluidic probe (MFP) facilitates performing local chemistry on biological substrates by confining nanoliter volumes of liquids. Using one particular implementation of the MFP, the hierarchical hydrodynamic flow confinement (hHFC), multiple liquids are simultaneously brought in contact with a substrate. Local chemical action and liquid shaping using the hHFC, is exploited to create cell patterns by locally lysing and removing cells. By utilizing the scanning ability of the MFP, user-defined patterns of cell monolayers are created. This protocol enables rapid, real-time and spatially controlled cell patterning, which can allow selective cell-cell and cell-matrix interaction studies.

We present a protocol to perform subtractive patterning of live cell monolayers on a surface. This is achieved by local and selective lysis of adherent cells using a microfluidic probe (MFP). The cell lysate retrieved from local regions can be used for downstream analysis, enabling molecular profiling studies.

The microfluidic probe (MFP) facilitates performing local chemistry on biological substrates by confining nanoliter volumes of liquids. Using one ...

Imaging Cell Viability on Non-transparent Scaffolds &#8212; Using the Example of a Novel Knitted Titanium Implant

Intervertebral disc degeneration and disc herniation is one of the major causes of lower back pain. Depletion of extracellular matrix, culminating in nucleus pulposus (NP) extrusion leads to intervertebral disc destruction. Currently available surgical treatments reduce the pain but do not restore the mechanical functionality of the spine. In order to preserve mechanical features of the spine, total disc or nucleus replacement thus became a wide interest. However, this arthroplasty era is still in an immature state, since none of the existing products have been clinically evaluated.
This study intends to test the biocompatibility of a novel nucleus implant made of knitted titanium wires. Despite all mechanical advantages, the material has its limits for conventional optical analysis as the resulting implant is non-transparent. Here we present a strategy that describes in vitro visualization, tracking and viability testing of osteochondro-progenitor cells on the scaffold. This protocol can be used to visualize the efficiency of the cleaning protocol as well as to investigate the biocompatibility of these and other non-transparent scaffolds. Furthermore, this protocol can be used to show adherence pattern of cells as well as cell viability and proliferation rates on/in the scaffold. This in vitro biocompatibility testing assay provides a propitious tool to analyze cell-material interaction in non-transparent and opaque scaffolds.

Here we present a fluorophore based imaging technique to detect cell viability on a non-transparent titanium scaffold as well as to detect glimpses of the scaffold impurities. This protocol troubleshoots the drawback of imaging cell-cell or cell-metal interactions on non-transparent scaffolds.

Intervertebral disc degeneration and disc herniation is one of the major causes of lower back pain. Depletion of extracellular matrix, culminating in ...

A Versatile Method of Patterning Proteins and Cells

Substrate and cell patterning techniques are widely used in cell biology to study cell-to-cell and cell-to-substrate interactions. Conventional patterning techniques work well only with simple shapes, small areas and selected bio-materials. This article describes a method to distribute cell suspensions as well as substrate solutions into complex, long, closed (dead-end) polydimethylsiloxane (PDMS) microchannels using negative pressure. This method enables researchers to pattern multiple substrates including fibronectin, collagen, antibodies (Sal-1), poly-D-lysine (PDL), and laminin. Patterning of substrates allows one to indirectly pattern a variety of cells. We have tested C2C12 myoblasts, the PC12 neuronal cell line, embryonic rat cortical neurons, and amphibian retinal neurons. In addition, we demonstrate that this technique can directly pattern fibroblasts in microfluidic channels via brief application of a low vacuum on cell suspensions. The low vacuum does not significantly decrease cell viability as shown by cell viability assays. Modifications are discussed for application of the method to different cell and substrate types. This technique allows researchers to pattern cells and proteins in specific patterns without the need for exotic materials or equipment and can be done in any laboratory with a vacuum.

This report describes a simple, easy to perform technique, using low pressure vacuum, to fill microfluidic channels with cells and substrates for biological research.

Substrate and cell patterning techniques are widely used in cell biology to study cell-to-cell and cell-to-substrate interactions. Conventional patterning ...

Microdissection of Primary Renal Tissue Segments and Incorporation with Novel Scaffold-free Construct Technology

Kidney transplantation is now a mainstream therapy for end-stage renal disease. However, with approximately 96,000 people on the waiting list and only one-fourth of these patients achieving transplantation, there is a dire need for alternatives for those with failing organs. In order to decrease the harmful consequences of dialysis along with the overall healthcare costs it incurs, active investigation is ongoing in search of alternative solutions to organ transplantation. Implantable tissue-engineered renal cellular constructs are one such feasible approach to replacing lost renal functionality. Here, described for the first time, is the microdissection of murine kidneys for isolation of living corticomedullary renal segments. These segments are capable of rapid incorporation within scaffold-free endothelial-fibroblast constructs which may enable rapid connection with host vasculature once implanted. Adult mouse kidneys were procured from living donors, followed by stereoscope microdissection to obtain renal segments 200 - 300 &#181;m in diameter. Multiple renal constructs were fabricated using primary renal segments harvested from only one kidney. This method demonstrates a procedure which could salvage functional renal tissue from organs that would otherwise be discarded.

Tissue-engineered renal constructs provide a solution for the organ shortage and deleterious effects of dialysis. Here, we describe a protocol to micro dissect murine kidneys for isolation of cortico-medullary segments. These segments are implanted into scaffold-free cellular constructs, forming renal organoids.

Kidney transplantation is now a mainstream therapy for end-stage renal disease. However, with approximately 96,000 people on the waiting list and only ...