The authors wish to acknowledge funding from the European Regional Development Fund &#8211; FNUSA-ICRC (no. CZ.1.05/ 1.1.00/ 02.0123), the American Heart Association Scientist Development Grant (AHA #06-35185N), and the National Institutes of Health (NIH #T32HL007111).

1. Synthesis of Magnetite Gel
<ol>
	<li>Wash all glassware by using concentrated hydrochloric acid followed by deionized water followed by ethyl alcohol. Allow to dry O/N, preferably in a drying oven. 
	CAUTION! hydrochloric acid is harmful &#8211; wear personal protective equipment and work in a fume hood; ethyl alcohol is harmful &#8211; wear personal protective equipment.</li>
	<li>Use a Dreschel bottle to de-gas 500 ml of deionized H2O by gently bubbling N2 gas for 30 mins.</li>
	<li>Set-up the magnetite synthesis apparatus within a chemical fume hood.
	<ol>
		<li>Place a 500 ml three-neck round-bottom flask within an isomantle heater&#160;and secure the center neck using a clamp and stand.</li>
		<li>Install a rubber septum into one of the round-bottom flask&#8217;s side necks and a reflux condenser with a rubber septum into the remaining side neck. Continuously run cold water through the reflux condenser.</li>
		<li>Puncture the round-bottom flask&#8217;s rubber septum with a needle connected to an N2 gas line and puncture the reflux condenser&#8217;s rubber septum with a needle connected to a gas line running to a bubbler (i.e., flask with water) to visualize gas outflow.</li>
		<li>Install a blade paddle into the round-bottom flask&#8217;s center neck via a paddle adapter. Attach the blade paddle&#8217;s shaft to an overhead stirrer mounted onto a stand.</li>
	</ol>
	</li>
	<li>Purge the round-bottom flask with N2 gas and leave N2 gas flowing at a low but detectable rate.</li>
	<li>Remove the reflux condenser from the round-bottom flask and add 1.000 g of iron(III) chloride, 0.6125 g of iron(II) chloride tetrahydrate, and 50 ml of de-gassed H2O. 
	CAUTION! iron(III) chloride and iron(II) chloride tetrahydrate&#160;are harmful &#8211; wear personal protective equipment.</li>
	<li>Replace the reflux condenser and stir at 1,000 rpm while heating to 50 &#176;C. Stirring under these conditions produces 10 nm diameter magnetite nanoparticles.</li>
	<li>Once at 50 &#176;C, add 10 ml of 28% ammonium hydroxide solution by injecting through the rubber septum in the round-bottom flask while still stirring. 
	CAUTION! ammonium hydroxide is harmful &#8211; wear personal protective equipment. 
	NOTE: The ammonium hydroxide solution is used to precipitate the magnetite and the solution should turn black.</li>
	<li>Remove the rubber septum and N2 gas line from the round-bottom flask and heat to 90 &#176;C to boil off the ammonia gas while still stirring. 
	NOTE: It is optional to maintain the flow of N2 into the round-bottom flask by puncturing the reflux condenser&#8217;s rubber septum, however, oxidation of magnetite to maghemite is negligible during this step.</li>
	<li>Once at 90 &#176;C, add 1 ml of oleic acid to the round-bottom flask while still stirring. The oleic acid is used to coat the magnetite nanoparticles to form magnetite gel. 
	CAUTION! oleic acid is harmful &#8211; wear personal protective equipment.</li>
	<li>Replace the rubber septum and N2 gas line onto the round-bottom flask and remove the reflux condenser.</li>
	<li>Turn off heat and stir at 500 rpm for 2 hr.</li>
	<li>Remove the round-bottom flask from the isomantle heater and decant any remaining liquid while using a strong magnet held against the bottom of the flask to retain the magnetite gel. 
	CAUTION! handle the strong magnet with extreme care to avoid damage or injury.</li>
	<li>Allow magnetite gel to air-dry O/N (optional).</li>
</ol>
2. Purification of Magnetite Gel
<ol>
	<li>Add 40 ml of hexane into the round-bottom flask to dissolve the magnetite gel 
	CAUTION! hexane is harmful &#8211; wear personal protective equipment and work in a fume hood.</li>
	<li>Use a separatory funnel with 40 ml of de-gassed H2O to remove residual H2O from the magnetite solution.
	<ol>
		<li>Slowly pour the magnetite solution onto the H2O within the separatory funnel and gently swirl the two-phase liquid for 5 mins.</li>
		<li>Drain out and discard the lower aqueous fraction.</li>
		<li>Slowly add 40 ml of de-gassed H2O to the separatory funnel such that it settles beneath the magnetite solution and gently swirl and drain as before.</li>
		<li>Repeat to wash for a third time.</li>
	</ol>
	</li>
	<li>Transfer magnetite solution to an Erlenmeyer flask, add a few spatulas worth of anhydrous sodium sulfate, and swirl to remove any remaining residual H2O from the magnetite solution.</li>
	<li>Filter the magnetite solution through 1 &#181;m filter paper in a filter funnel to remove the sodium sulfate and residual H2O. 
	NOTE: Vacuum assistance is recommended.</li>
	<li>Transfer the magnetite solution to a 50 ml&#160;evaporating&#160;flask and use a rotary evaporator to evaporate the hexane for 2 h with the following conditions: moderate rotation speed, vacuum applied, evaporating&#160;flask in a 50 &#176;C water bath, and 24 &#176;C water circulating through the condenser. 
	NOTE: Optionally, store the magnetite gel prior to coating&#160;with PLGA.</li>
</ol>
3. Coating of Magnetite Nanoparticles with PLGA Shell
<ol>
	<li>Dissolve 3.60 g of PLGA (75/25 blend) in 240 ml of ethyl acetate to create a 1.5% (m/v) solution. CAUTION: ethyl acetate is harmful &#8211; wear personal protective equipment and work in a fume hood.</li>
	<li>Dissolve 25.00 g of Pluronic F-127 in 500 ml of de-gassed H2O using a magnetic stirrer to create a 5.0% (m/v) solution. 
	NOTE: Pluronic F-127 is a non-ionic amphiphilic block copolymer that acts as a biocompatible surfactant. It helps to stabilize the oil-in-water emulsion in step 3.3.2.</li>
	<li>Using a microspatula, collect the magnetite gel into six 0.040 g aliquots within weighted glass vials. Perform the following coating and washing process for each aliquot. 
	NOTE: The aliquots are necessary to ensure efficient handling and magnetic decantation, which will maximize purity and yield while minimizing degradation prior to freeze-drying in step 4.
	<ol>
		<li>Add a 0.040 g aliquot of magnetite gel and 40 ml of the PLGA solution to a plastic beaker and sonicate in an ultrasonic cleaner for 10 mins.</li>
		<li>Add 80 ml of the Pluronic solution to the plastic beaker and immediately emulsify with a laboratory mixer at the highest setting for 7 mins to form the PLGA coating on the magnetite nanoparticles as an oil-in-water emulsion.</li>
		<li>Immediately dilute the SPION solution in 1 L of deionized H2O and sonicate for 1 h in a chemical fume hood to evaporate the ethyl acetate.</li>
		<li>Place a strong magnet next to the SPION solution and gently stir to collect brownish SPIONs at the magnet. 
		NOTE: It may be necessary to intermittently stir for several hours before the solution turns whitish indicating that most of the SPIONs have been collected.</li>
		<li>Decant the aqueous solution while retaining the SPIONs in the beaker with the magnet.</li>
		<li>Wash the SPIONs three times as follows.
		<ol>
			<li>Suspend the SPIONs in 1 L of deionized H2O.</li>
			<li>Sonicate the SPION solution for 20 mins.</li>
			<li>Place a strong magnet next to the SPION solution and gently stir to collect brownish SPIONs at the magnet. It may be necessary to intermittently stir for several hours before the solution turns clear indicating that most of the SPIONs have been collected.</li>
			<li>Decant the aqueous solution while retaining the SPIONs in the beaker with the magnet.</li>
		</ol>
		</li>
	</ol>
	</li>
	<li>Collect the SPIONs synthesized from each of the six magnetite gel aliquots into a single weighted glass vial as an aqueous suspension. Optionally decant excess water magnetically as needed.</li>
</ol>
4. Freeze-drying of SPIONs
<ol>
	<li>Freeze the SPION solution.</li>
	<li>Freeze-dry the SPION solution O/N in a lyophilizer.</li>
	<li>Weigh the freeze-dried SPIONs. Freeze-dried SPIONs can be stored at -20 &#176;C until used for cell labeling. 
	NOTE: Storage at -20 &#176;C dramatically reduces degradation kinetics and increases shelf life.</li>
</ol>
5. Labeling of Cells with SPIONs
<ol>
	<li>Suspend an aliquot of SPIONs in phosphate-buffered saline (PBS) at a concentration of 40 mg/ml and sonicate for 30 mins.</li>
	<li>Add the SPION solution to a nearly confluent flask of cells at a concentration of 5 &#181;l/ml of cell culture medium. Ensure even distribution by gently rocking the flask.</li>
	<li>Incubate the cells for 16 hr at 37 &#176;C.</li>
	<li>Gently aspirate culture medium and wash cells twice with PBS.</li>
	<li>Collect magnetically-labeled cells and use for experiments.</li>
	<li>Unused SPION solution can be stored at 4 &#176;C and should be used within a few months. Sonicate for 30 mins before each use.</li>
</ol>

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The authors declare that they have no competing financial interests.

As with any nanoparticle synthesis protocol, the purity of the reactant chemicals is critical for achieving high quality SPIONs that will have minimal cytotoxic effects. It is therefore important to purchase very pure reagents including oleic acid (&#8805;99%), iron(II) chloride tetrahydrate (&#8805;99.99%), iron(III) chloride (&#8805;99.99%), ethyl acetate (HPLC grade, &#8805;99.9%), hexane (HPLC grade, &#8805;97.0%), ammonium hydroxide (&#8805;99.99%), and sodium sulfate (&#8805;99.0%). It is of particular importance to purchase very pure and high quality PLGA, which can be relatively expensive. In addition, all glassware must be thoroughly washed with hydrochloric acid, deionized water, and ethyl alcohol and allowed to dry before use.
Similarly, the purification and washing steps within the protocol are critical to ensure the final SPIONs will be of high quality and have minimal cytotoxic effects. The magnetite gel must be free of as much ammonium hydroxide, water, and hexane as possible before coating with PLGA. Accordingly, much of the protocol is devoted to ensuring the purity of the magnetite gel. Subsequently, the PLGA-magnetite SPIONs must be free of ethyl acetate, Pluronic, and excess PLGA. The final SPION washing steps are the most time consuming portion of the protocol, but must be completed to ensure high purity. Specifically, magnetic collection of the particles during each washing step can be very time consuming. Stirring the solution can greatly increase the speed of particle collection, but magnetic stir bars cannot be used. Overhead stirrers operating at a low speed are the most effective means for rapid particle collection. Ensure a large brownish collection of SPIONs appears at the magnet and the solution appears white or clear before decanting. This can often require several hours of stirring, but will result in a higher final yield. The magnetic decantation steps also serve to ensure only magnetic particles are retained while all non-magnetic materials are discarded.
Excessive iron levels can be cytotoxic, so the amount of magnetic mass that can be imparted to a cell using this technique is limited. The concentration of iron may need to be decreased for particularly sensitive cell types or increased for particularly weak magnetic fields, but the protocol described here provides a proven starting point to balance safety and efficacy. The SPIONs synthesized by this protocol are made from a solution with a 1:15 ratio by mass of magnetite to PLGA and the SPIONs are introduced to cells at a concentration of 200 &#181;g/ml of cell culture medium. Either of these parameters can be adjusted to alter the quantity of iron endocytosed by each cell as necessary.
SPIONs are safe for human implantation and will biodegrade over time (half-life of approximately 40-50 days)31. Both the magnetite and PLGA form harmless degradation products and are cleared from the body via natural pathways32. The biodegradable nature of the SPIONs means any cytotoxic effects will diminish with time, but also limits the potential applications to those that do not require cells to maintain their magnetic properties beyond a few months. SPIONs also have the advantage of labeling cells and imparting their magnetic effects without the need for surface proteins nor targeting ligands that are susceptible to the formation of a protein corona upon exposure to the biological milieu33,34.
Imparting magnetic properties to cells is useful for a broad array of biomedical applications requiring targeted cell delivery or sorting29. A variety of cell types have demonstrated the ability to safely endocytose SPIONs including mesenchymal stem cells35, endothelial progenitor cells36, beta islet cells37, and neural stem cells38. Magnetic cell targeting may be preferred over other cell targeting techniques when a high degree of control over the delivery conditions is necessary.

Targeted delivery and capture of cells to specific sites within the body is desirable for a variety of biomedical applications. Delivery of neural stem cells to the brain by MRI-guided focused ultrasound has been proposed as a possible treatment option for neurodegenerative disease, traumatic brain injury, and stroke1. Mesenchymal stem cells are being studied for their ability to deliver anti-cancer drugs to tumors due to their natural tumor-tropic properties2,3. Cardiac stem cells have been delivered to the heart as a possible treatment for myocardial infarction4,5. Vascular stents have been developed with CD34 antibodies to capture circulating progenitor cells6. While promising, these cell targeting approaches present drawbacks including lack of cell specificity, inconsistent cell retention, and off-target cell delivery.
The overall goal of the current method is to enable magnetically directed targeting of cells for a variety of cell delivery and sorting applications. Magnetic targeting allows for controlled delivery of specific cells to a specific target site with minimal off-target effects7. The magnetic fields can be generated by implanted or external devices to safely direct the movement of magnetically-labeled cells within the body8. Numerous research efforts have focused on magnetically directed targeting of stem cells to injured tissues such as the heart9-14, retina15, lung16, skin17, spinal cord18,19, bone20, liver21, and muscle22,23 in order to improve regeneration outcomes.
Magnetic targeting of cells has also been studied extensively as a means to endothelialize implantable cardiovascular devices. A uniform and complete endothelium provides a barrier between the device and circulating blood elements to mitigate thrombosis and inflammation. Endothelial cells can be delivered to the device either prior to implantation or via the vascular system following implantation. In both cases, magnetic fields are used to capture cells to the surface of the device and retain the cells when subjected to the shear stress generated by circulating blood. Magnetic vascular stents24-27 and vascular grafts28 have both been fabricated and tested for this purpose.
Magnetic cell targeting requires a strategy for labeling cells with magnetic carrier particles. These particles can be bound to the surface of cells via antibodies or ligand/receptor pairs or they can be endocytosed into the cells. Superparamagnetic iron oxide nanoparticles (SPION) are biodegradable, biocompatible, and readily endocytosed by a variety of cell types29. These particles effectively render a cell responsive to magnetic fields and are naturally degraded over time. SPIONs provide a straightforward and safe means of magnetically labeling cells in culture for a variety of magnetic targeting and sorting applications. A method for synthesizing SPIONs with a magnetite (Fe3O4) core and poly(lactic-co-glycolic acid) (PLGA) shell is provided. In addition, a method for labeling cells in culture with SPIONs is provided.

<table><tbody><tr><td>Ammonium Hydroxide solution, 28% NH&lt;sub&gt;3&lt;/sub&gt; in H&lt;sub&gt;2&lt;/sub&gt;O, &amp;ge;99.99% trace metal basis</td><td>Sigma-Aldrich</td><td>338818-100ML&amp;nbsp;</td><td>Harmful reagent - wear personal protective equipment</td></tr><tr><td>Dreschel bottle, 500 ml</td><td>Ace Glass</td><td>5516-16</td><td></td></tr><tr><td>Ethyl Acetate, CHROMASOLVR Plus, for HPLC, 99.9%&amp;nbsp;</td><td>Sigma-Aldrich</td><td>650528-1L</td><td>Harmful reagent - wear personal protective equipment &amp;amp; work in fume hood</td></tr><tr><td>Ethyl alcohol</td><td>Sigma-Aldrich</td><td>E7023</td><td>Harmful reagent - wear personal protective equipment</td></tr><tr><td>Evaporating flask, 50 ml, 24/40 joint</td><td>Sigma-Aldrich</td><td>Z515558</td><td>For use with rotoevaporator</td></tr><tr><td>Filter paper, 3 cm dia, grade 1</td><td>Fisher</td><td>09-805P</td><td>For use with glass filter funnel</td></tr><tr><td>Glass beakers, 1 L</td><td>Fisher</td><td>FB-101-1000</td><td>For washing SPIONs</td></tr><tr><td>Glass filter funnel, vacuum hose adapter, fits 24/40, 30 mL</td><td>Fisher</td><td>K954100-0344&amp;nbsp;</td><td></td></tr><tr><td>Glass vial caps</td><td>Fisher</td><td>03-391-46</td><td>For use with glass vials</td></tr><tr><td>Glass vials, 2 ml</td><td>Fisher</td><td>03-391-44</td><td>For collecting magnetite gel &amp;amp; SPIONs</td></tr><tr><td>Hexane, CHROMASOLVR, for HPLC, &amp;ge;97.0% (GC)</td><td>Sigma-Aldrich</td><td>34859-1L&amp;nbsp;</td><td>Harmful reagent - wear personal protective equipment &amp;amp; work in fume hood</td></tr><tr><td>Hydrochloric acid</td><td>Sigma-Aldrich</td><td>H1758</td><td>Harmful reagent - wear personal protective equipment &amp;amp; work in fume hood</td></tr><tr><td>Iron(II) chloride tetrahydrate, &amp;ge;99.99% trace metals basis&amp;nbsp;</td><td>Sigma-Aldrich</td><td>380024-5G</td><td>Harmful reagent - wear personal protective equipment</td></tr><tr><td>Iron(III) chloride anhydrous, powder, &amp;ge;99.99% trace metals basis</td><td>Sigma-Aldrich</td><td>451649-1G</td><td>Harmful reagent - wear personal protective equipment</td></tr><tr><td>Isomantle heater, 500 mL</td><td>Voight Global</td><td>EM0500/CEX1</td><td></td></tr><tr><td>Laboratory mixer</td><td>Silverson</td><td>L5M-A</td><td></td></tr><tr><td>Lyophilizer</td><td>Labconco</td><td>7670520</td><td></td></tr><tr><td>Microspatulas</td><td>Fisher</td><td>21-401-25A</td><td>For transfering magnetite gel</td></tr><tr><td>NdFeB magnet, 1 in x 1 in x 1 in</td><td>Amazing Magnets</td><td>C1000H-M</td><td>Very strong magnet, handle with care</td></tr><tr><td>Oleic acid, &amp;ge;99% (GC)</td><td>Sigma-Aldrich</td><td>O1008-5G&amp;nbsp;</td><td>Store in freezer; Harmful reagent - wear personal protective equipment</td></tr><tr><td>Overhead stirrer</td><td>IKA</td><td>2572201</td><td></td></tr><tr><td>Overhead stirrer clamp</td><td>IKA</td><td>2664000</td><td>For use with overhead stirrer</td></tr><tr><td>Overhead stirrer H-stand</td><td>IKA</td><td>1412000</td><td>For use with overhead stirrer</td></tr><tr><td>Phosphate buffered saline</td><td>Life Technologies</td><td>10010-023</td><td></td></tr><tr><td>Plastic beakers, 250 ml</td><td>Fisher</td><td>02-591-28</td><td></td></tr><tr><td>PLGA PURASORB PDLG (75/25 blend)</td><td>Purac</td><td>PDLG 7502</td><td>PDLG 7502A may be used as well; Store in freezer</td></tr><tr><td>Pluronic F-127 powder, BioReagent, suitable for cell culture</td><td>Sigma-Aldrich</td><td>P2443-250G&amp;nbsp;</td><td></td></tr><tr><td>PTFE expandable blade paddle, 8 mm dia</td><td>SciQuip</td><td>SP4018</td><td></td></tr><tr><td>PTFE vessel adapter, fits 24/40, 8 mm dia paddle</td><td>Monmouth Scientific</td><td>PTFE Vessel Adaptor A480</td><td>For use with PTFE expandable blade paddle</td></tr><tr><td>Recirculating chiller</td><td>Clarkson</td><td>696613</td><td>For use with rotoevaporator</td></tr><tr><td>Reflux condenser, fits 24/40, 250 mm</td><td>Ace Glass</td><td>5997-133</td><td></td></tr><tr><td>Rotoevaporator</td><td>Clarkson</td><td>216949</td><td></td></tr><tr><td>Rubber septa, fits 24/40</td><td>Ace Glass</td><td>9096-56</td><td></td></tr><tr><td>Separatory funnel with stopper, 250 ml</td><td>Fisher</td><td>10-438E</td><td></td></tr><tr><td>Sodium sulfate ACS reagent, &amp;ge;99.0%, anhydrous, granular</td><td>Sigma-Aldrich</td><td>239313-500G&amp;nbsp;</td><td></td></tr><tr><td>Three neck round bottom flask, angled, 24/40 joints, 500 ml</td><td>Ace Glass</td><td>6948-16</td><td></td></tr><tr><td>Ultrasonic cleaner perforated pan</td><td>Fisher</td><td>15-335-20A</td><td>For use with ultrasonic cleaner</td></tr><tr><td>Ultrasonic cleaner, 2.8 L</td><td>Fisher</td><td>15-335-20</td><td></td></tr><tr><td>Vacuum controller</td><td>Clarkson</td><td>216639</td><td>For use with rotoevaporator (optional)</td></tr><tr><td>Vacuum pump</td><td>Clarkson</td><td>219959</td><td>For use with rotoevaporator</td></tr></tbody></table>

cell labeling and targeting with superparamagnetic iron oxide nanoparticles

Targeted delivery of cells and therapeutic agents would benefit a wide range of biomedical applications by concentrating the therapeutic effect at the target site while minimizing deleterious effects to off-target sites. Magnetic cell targeting is an efficient, safe, and straightforward delivery technique. Superparamagnetic iron oxide nanoparticles (SPION) are biodegradable, biocompatible, and can be endocytosed into cells to render them responsive to magnetic fields. The synthesis process involves creating magnetite (Fe3O4) nanoparticles followed by high-speed emulsification to form a poly(lactic-co-glycolic acid) (PLGA) coating. The PLGA-magnetite SPIONs are approximately 120 nm in diameter including the approximately 10 nm diameter magnetite core. When placed in culture medium, SPIONs are naturally endocytosed by cells and stored as small clusters within cytoplasmic endosomes. These particles impart sufficient magnetic mass to the cells to allow for targeting within magnetic fields. Numerous cell sorting and targeting applications are enabled by rendering various cell types responsive to magnetic fields. SPIONs have a variety of other biomedical applications as well including use as a medical imaging contrast agent, targeted drug or gene delivery, diagnostic assays, and generation of local hyperthermia for tumor therapy or tissue soldering.

Magnetite nanoparticles are approximately 10 nm in diameter as a result of stirring an aqueous solution of iron(III) chloride and iron(II) chloride tetrahydrate at 50 &#176;C and 1,000 rpm (Figure 1). These results demonstrate successful synthesis of magnetite nanoparticles. It is important to verify the size and shape of magnetite nanoparticles taken from a small sample of the batch when attempting the synthesis for the first time. Transmission electron microscopy (TEM) is the preferred method for visualizing these particles. The batch should be discarded and the synthesis should be attempted again if the magnetite nanoparticles are not approximately 10 nm in diameter and spherical as shown in Figure 1.
Coating the magnetite nanoparticles with PLGA using a high-speed emulsifier results in PLGA-magnetite SPIONs with a diameter of 120 nm (Figure 2). These results demonstrate successful synthesis of PLGA-magnetite SPIONs. It is important to verify the size and shape of PLGA-magnetite SPIONs taken from a small sample of the batch when attempting the synthesis for the first time. Scanning electron microscopy (SEM) is the preferred method for visualizing these particles. The batch should be discarded and the synthesis should be attempted again if the PLGA-magnetite SPIONs are not approximately 120 nm in diameter and spherical as shown in Figure 2. While larger or smaller particles may be desirable for certain applications, the composition will be unknown and therefore cell labeling, magnetic susceptibility, and cytotoxicity will be unpredictable.
Incubation of blood outgrowth endothelial cells with SPIONs for 16 hr results in endocytosis of the nanoparticles (Figure 3). These results demonstrate successful labeling of cells with SPIONs. It is important to verify the presence of SPIONs within cells taken from a small sample of the batch when attempting the labeling for the first time. Transmission electron microscopy is the preferred method for visualizing these SPION-labeled cells. The cells should be discarded and the labeling should be attempted again if the PLGA-mangetite SPIONs do not appear as round black particles clustered together within cytoplasmic endosomes as shown in Figure 3. Furthermore, lower concentrations of SPIONs may fail to enable magnetic cell targeting and higher concentrations of SPIONs may be cytotoxic. If necessary, the concentration of SPIONs used to label cells can be adjusted accordingly.
The quantity of iron loaded into the cells is sufficient to achieve magnetic capture of viable cells to ferromagnetic implantable medical devices (Figure 4). These results demonstrate successful SPION-mediated magnetic cell targeting. If a stronger cell targeting effect is desired, the preferred strategy is to increase the strength or gradient of the generated or applied magnetic field8,30. Increasing the concentration of SPIONs used to label cells should only be tried as a last resort due to cytotoxicity concerns. If improved cell viability is desired, the concentration of SPIONs used to label cells should be decreased.
<img alt="Figure 1" src="/files/ftp_upload/53099/53099fig1.jpg" /> 
Figure 1.&#160;TEM image of magnetite nanoparticles.&#160;Magnetite nanoparticles are approximately 10 nm in diameter as seen by transmission electron microscopy (TEM). Particles are spherical and uniform in size. Scale bar = 100 nm. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53099/53099fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/53099/53099fig2.jpg" /> 
Figure 2.&#160;SEM image of PLGA-magnetite SPIONs.&#160;PLGA-coated magnetite SPIONs are approximately 120 nm in diameter as seen by scanning electron microscopy (SEM). Particles are spherical and uniform in size. Scale bar = 500 &#181;m. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53099/53099fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" src="/files/ftp_upload/53099/53099fig3.jpg" /> 
Figure 3.&#160;TEM image of a magnetically-labeled endothelial cell.&#160;A magnetically-labeled blood outgrowth endothelial cell visualized by transmission&#160;electron microscopy (TEM). The SPIONs are naturally endocytosed by the cells and stored in small clusters within cytoplasmic endosomes. Left scale bar = 2 &#181;m and right scale bar = 0.5 &#181;m. Re-print with permission from24. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53099/53099fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" src="/files/ftp_upload/53099/53099fig4.jpg" /> 
Figure 4.&#160;Fluorescence microscopy image of magnetic cell capture.&#160;Magnetically-labeled endothelial cells are attracted to a ferromagnetic vascular stent (right) at a significantly higher rate than a non-magnetic stent (left). Scale bars = 100 &#181;m. Re-print with permission from24. <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53099/53099fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>

Watch this Scientific Journal Video about Cell Labeling and Targeting with Superparamagnetic Iron Oxide Nanoparticles at JoVE.com

Cell Labeling and Targeting with Superparamagnetic Iron Oxide Nanoparticles

Targeted cell delivery is useful in a variety of biomedical applications. The goal of this protocol is to use superparamagnetic iron oxide nanoparticles (SPION) to label cells and thereby enable magnetic cell targeting approaches for a high degree of control over cell delivery and localization.

Targeted delivery of cells and therapeutic agents would benefit a wide range of biomedical applications by concentrating the therapeutic effect at the ...

cell-labeling-targeting-with-superparamagnetic-iron-oxide

Nanyang Technological University

Research

JoVE Journal

Bioengineering

12.0K Views.  Mayo Clinic. Targeted cell delivery is useful in a variety of biomedical applications. The goal of this protocol is to use superparamagnetic iron oxide nanoparticles (SPION) to label cells and thereby enable magnetic cell targeting approaches for a high degree of control over cell delivery and localization.

Video: Cell Labeling and Targeting with Superparamagnetic Iron Oxide Nanoparticles

Registered Bioimaging of Nanomaterials for Diagnostic and Therapeutic Monitoring

Nanomedications can be carried by blood borne monocyte-macrophages into the reticuloendothelial system (RES; spleen, liver, lymph nodes) and to end organs. The latter include the lung, RES, and brain and are operative during human immunodeficiency virus type one (HIV-1) infection. Macrophage entry into tissues is notable in areas of active HIV-1 replication and sites of inflammation. In order to assess the potential of macrophages as nanocarriers, superparamagnetic iron-oxide and/or drug laden particles coated with surfactants were parenterally injected into HIV-1 encephalitic mice. This was done to quantitatively assess particle and drug biodistribution. Magnetic resonance imaging (MRI) test results were validated by histological coregistration and enhanced image processing. End organ disease as typified by altered brain histology were assessed by MRI. The demonstration of robust migration of nanoformulations into areas of focal encephalitis provides '"proof of concept" for the use of advanced bioimaging techniques to monitor macrophage migration. Importantly, histopathological aberrations in brain correlate with bioimaging parameters making the general utility of MRI in studies of cell distribution in disease feasible. We posit that using such methods can provide a real time index of disease burden and therapeutic efficacy with translational potential to humans.

Bioimaging methods used to assess cell biodistribution of nanoparticles are applicable for therapeutic and diagnostic monitoring of nanoformulated compounds. The methods described herein are sensitive and specific when assessed by histological coregistration. The methodologies provide a translational pathway from rodent to human applications.

Nanomedications can be carried by blood borne monocyte-macrophages into the reticuloendothelial system (RES; spleen, liver, lymph nodes) and to end ...

Labeling Stem Cells with Ferumoxytol, an FDA-Approved Iron Oxide Nanoparticle

Stem cell based therapies offer significant potential for the field of regenerative medicine. However, much remains to be understood regarding the in vivo kinetics of transplanted cells. A non-invasive method to repetitively monitor transplanted stem cells in vivo would allow investigators to directly monitor stem cell transplants and identify successful or unsuccessful engraftment outcomes.
A wide range of stem cells continues to be investigated for countless applications. This protocol focuses on 3 different stem cell populations: human embryonic kidney 293 (HEK293) cells, human mesenchymal stem cells (hMSC) and induced pluripotent stem (iPS) cells. HEK 293 cells are derived from human embryonic kidney cells grown in culture with sheared adenovirus 5 DNA. These cells are widely used in research because they are easily cultured, grow quickly and are easily transfected. hMSCs are found in adult marrow. These cells can be replicated as undifferentiated cells while maintaining multipotency or the potential to differentiate into a limited number of cell fates. hMSCs can differentiate to lineages of mesenchymal tissues, including osteoblasts, adipocytes, chondrocytes, tendon, muscle, and marrow stroma. iPS cells are genetically reprogrammed adult cells that have been modified to express genes and factors similar to defining properties of embryonic stem cells. These cells are pluripotent meaning they have the capacity to differentiate into all cell lineages 1. Both hMSCs and iPS cells have demonstrated tissue regenerative capacity in-vivo.
Magnetic resonance (MR) imaging together with the use of superparamagnetic iron oxide (SPIO) nanoparticle cell labels have proven effective for in vivo tracking of stem cells due to the near microscopic anatomical resolution, a longer blood half-life that permits longitudinal imaging and the high sensitivity for cell detection provided by MR imaging of SPIO nanoparticles 2-4. In addition, MR imaging with the use of SPIOs is clinically translatable. SPIOs are composed of an iron oxide core with a dextran, carboxydextran or starch surface coat that serves to contain the bioreactive iron core from plasma components. These agents create local magnetic field inhomogeneities that lead to a decreased signal on T2-weighted MR images 5. Unfortunately, SPIOs are no longer being manufactured. Second generation, ultrasmall SPIOs (USPIO), however, offer a viable alternative. Ferumoxytol (FerahemeTM) is one USPIO composed of a non-stoichiometric magnetite core surrounded by a polyglucose sorbitol carboxymethylether coat. The colloidal, particle size of ferumoxytol is 17-30 nm as determined by light scattering. The molecular weight is 750 kDa, and the relaxivity constant at 2T MRI field is 58.609 mM-1 sec-1 strength4. Ferumoxytol was recently FDA-approved as an iron supplement for treatment of iron deficiency in patients with renal failure 6. Our group has applied this agent in an &ldquo;off label&rdquo; use for cell labeling applications. Our technique demonstrates efficient labeling of stem cells with ferumoxytol that leads to significant MR signal effects of labeled cells on MR images. This technique may be applied for non-invasive monitoring of stem cell therapies in pre-clinical and clinical settings.

We describe a technique for labeling and tracking stem cells with FDA-approved, superparamagnetic iron oxide (SPIO), ferumoxytol (Feraheme). This cellular imaging technique that utilizes magnetic resonance (MR) imaging for visualization, is readily accessible for long-term monitoring and diagnosis of successful or unsuccessful stem cell engraftments in patients.

Stem cell based therapies offer significant potential for the field of regenerative medicine. However, much remains to be understood regarding the in vivo ...

Medicine

Labeling hESCs and hMSCs with Iron Oxide Nanoparticles for Non-Invasive in vivo Tracking with MR Imaging

In recent years, stem cell research has led to a better understanding of developmental biology, various diseases and its potential impact on regenerative medicine. A non-invasive method to monitor the transplanted stem cells repeatedly in vivo would greatly enhance our ability to understand the mechanisms that control stem cell death and identify trophic factors and signaling pathways that improve stem cell engraftment. MR imaging has been proven to be an effective tool for the in vivo depiction of stem cells with near microscopic anatomical resolution. In order to detect stem cells with MR, the cells have to be labeled with cell specific MR contrast agents. For this purpose, iron oxide nanoparticles, such as superparamagnetic iron oxide particles (SPIO), are applied, because of their high sensitivity for cell detection and their excellent biocompatibility. SPIO particles are composed of an iron oxide core and a dextran, carboxydextran or starch coat, and function by creating local field inhomogeneities, that cause a decreased signal on T2-weighted MR images. This presentation will demonstrate techniques for labeling of stem cells with clinically applicable MR contrast agents for subsequent non-invasive in vivo tracking of the labeled cells with MR imaging.

For the evaluation of new stem cell therapies it is important to non-invasively track the injected cells in vivo. This video will show you how to label human mesenchymal and embryonic stem cells with iron oxide based contrast agents in vivo for subsequent MR imaging in vivo.

In recent years, stem cell research has led to a better understanding of developmental biology, various diseases and its potential impact on regenerative ...

Biology

Multimodal Imaging of Stem Cell Implantation in the Central Nervous System of Mice

During the past decade, stem cell transplantation has gained increasing interest as primary or secondary therapeutic modality for a variety of diseases, both in preclinical and clinical studies. However, to date results regarding functional outcome and/or tissue regeneration following stem cell transplantation are quite diverse. Generally, a clinical benefit is observed without profound understanding of the underlying mechanism(s)1. Therefore, multiple efforts have led to the development of different molecular imaging modalities to monitor stem cell grafting with the ultimate aim to accurately evaluate survival, fate and physiology of grafted stem cells and/or their micro-environment. Changes observed in one or more parameters determined by molecular imaging might be related to the observed clinical effect. In this context, our studies focus on the combined use of bioluminescence imaging (BLI), magnetic resonance imaging (MRI) and histological analysis to evaluate stem cell grafting.
BLI is commonly used to non-invasively perform cell tracking and monitor cell survival in time following transplantation2-7, based on a biochemical reaction where cells expressing the Luciferase-reporter gene are able to emit light following interaction with its substrate (e.g. D-luciferin)8, 9. MRI on the other hand is a non-invasive technique which is clinically applicable10 and can be used to precisely locate cellular grafts with very high resolution11-15, although its sensitivity highly depends on the contrast generated after cell labeling with an MRI contrast agent. Finally, post-mortem histological analysis is the method of choice to validate research results obtained with non-invasive techniques with highest resolution and sensitivity. Moreover end-point histological analysis allows us to perform detailed phenotypic analysis of grafted cells and/or the surrounding tissue, based on the use of fluorescent reporter proteins and/or direct cell labeling with specific antibodies.
In summary, we here visually demonstrate the complementarities of BLI, MRI and histology to unravel different stem cell- and/or environment-associated characteristics following stem cell grafting in the CNS of mice. As an example, bone marrow-derived stromal cells, genetically engineered to express the enhanced Green Fluorescent Protein (eGFP) and firefly Luciferase (fLuc), and labeled with blue fluorescent micron-sized iron oxide particles (MPIOs), will be grafted in the CNS of immune-competent mice and outcome will be monitored by BLI, MRI and histology (Figure 1).

This article describes an optimized sequence of events for multimodal imaging of cellular grafts in rodent brain using: (i) in vivo bioluminescence and magnetic resonance imaging, and (ii) post mortem histological analysis. Combining these imaging modalities on a single animal allows cellular graft evaluation with high resolution, sensitivity and specificity.

During the past decade, stem cell transplantation has gained increasing interest as primary or secondary therapeutic modality for a variety of diseases, ...

Neuroscience

Synthesis of Cationized Magnetoferritin for Ultra-fast Magnetization of Cells

Many important biomedical applications, such as cell imaging and remote manipulation, can be achieved by labeling cells with superparamagnetic iron oxide nanoparticles (SPIONs). Achieving sufficient cellular uptake of SPIONs is a challenge that has traditionally been met by exposing cells to elevated concentrations of SPIONs or by prolonging exposure times (up to 72 hr). However, these strategies are likely to mediate toxicity. Here, we present the synthesis of the protein-based SPION magnetoferritin as well as a facile surface functionalization protocol that enables rapid cell magnetization using low exposure concentrations. The SPION core of magnetoferritin consists of cobalt-doped iron oxide with an average particle diameter of 8.2 nm mineralized inside the cavity of horse spleen apo-ferritin. Chemical cationization of magnetoferritin produced a novel, highly membrane-active SPION that magnetized human mesenchymal stem cells (hMSCs) using incubation times as short as one minute and iron concentrations as lows as 0.2 mM.

A protocol for the synthesis and cationization of cobalt-doped magnetoferritin is presented, as well as a method to rapidly magnetize stem cells with cationized magnetoferritin.

Many important biomedical applications, such as cell imaging and remote manipulation, can be achieved by labeling cells with superparamagnetic iron oxide ...

Iron Oxide Nanoparticles for Image-Guided Therapy Delivery in Murine Glioblastoma

Nanoparticle Delivery of an Oligonucleotide Payload in a Glioblastoma Multiforme Animal Model

Glioblastoma multiforme (GBM) is the most common and aggressive form of primary brain malignancy for which there is no cure. The blood-brain barrier is a significant hurdle in the delivery of therapies to GBM. Reported here is an image-guided, iron oxide-based therapeutic delivery nano platform capable of bypassing this physiological barrier by virtue of size and accumulating in the tumor region, delivering its payload. This 25 nm nano platform consists of crosslinked dextran-coated iron oxide nanoparticles labeled with Cy5.5 fluorescent dye and containing antisense oligonucleotide as a payload. The magnetic iron oxide core enables tracking of the nanoparticles through in vivo magnetic resonance imaging, while Cy5.5 dye allows tracking by optical imaging. This report details the monitoring of the accumulation of this nanoparticle platform (termed MN-anti-miR10b) in orthotopically implanted glioblastoma tumors following intravenous injection. In addition, it provides insight into the in vivo delivery of RNA oligonucleotides, a problem that has hampered the translation of RNA therapeutics into the clinic.

Author Spotlight: Innovative Cancer Therapies with Iron Oxide Nanoparticles for Glioblastoma Treatment

The blood-brain barrier is a significant hurdle in the delivery of therapies for glioblastoma, a disease for which there is no cure. Here, we report an in vivo image-guided iron oxide therapeutic nano platform that can bypass this physiological barrier by virtue of size and accumulate in the tumor.

Glioblastoma multiforme (GBM) is the most common and aggressive form of primary brain malignancy for which there is no cure. The blood-brain barrier is a ...

Cancer Research

Using Magnetometry to Monitor Cellular Incorporation and Subsequent Biodegradation of Chemically Synthetized Iron Oxide Nanoparticles

Magnetic nanoparticles, made of iron oxide, present a peculiar interest for a wide range of biomedical applications for which they are often internalized in cells and then left within. One challenge is to assess their fate in the intracellular environment with reliable and precise methodologies. Herein, we introduce the use of the vibrating sample magnetometer (VSM) to precisely quantify the integrity of magnetic nanoparticles within cells by measuring their magnetic moment. Stem cells are first labeled with two types of magnetic nanoparticles; the nanoparticles have the same core produced via a fast and efficient microwave-based nonaqueous sol gel synthesis and differ in their coating: the commonly used citric acid molecule is compared to polyacrylic acid. The formation of 3D cell-spheroids is then achieved via centrifugation and the magnetic moment of these spheroids is measured at different times with the VSM. The obtained moment is a direct fingerprint of the nanoparticles&#8217; integrity, with decreasing values indicative of a nanoparticle degradation. For both nanoparticles, the magnetic moment decreases over culture time revealing their biodegradation. A protective effect of the polyacrylic acid coating is also shown, when compared to citric acid.

Iron oxide nanoparticles are synthesized via a nonaqueous sol gel procedure and coated with anionic short molecules or polymer. The use of magnetometry for monitoring the incorporation and biotransformations of magnetic nanoparticles inside human stem cells is demonstrated using a vibrating sample magnetometer (VSM).

Magnetic nanoparticles, made of iron oxide, present a peculiar interest for a wide range of biomedical applications for which they are often internalized ...

Biofunctionalization of Magnetic Nanomaterials

Magnetic nanomaterials have received great attention in different biomedical applications. Biofunctionalizing these nanomaterials with specific targeting agents is a crucial aspect to enhance their efficacy in diagnostics and treatments while minimizing the side effects. The benefit of magnetic nanomaterials compared to non-magnetic ones is their ability to respond to magnetic fields in a contact-free manner and over large distances. This allows to guide or accumulate them, while they can also be monitored. Recently, magnetic nanowires (NWs) with unique features were developed for biomedical applications. The large magnetic moment of these NWs enables a more efficient remote control of their movement by a magnetic field. This has been utilized with great success in cancer treatment, drug delivery, cell tracing, stem cell differentiation or magnetic resonance imaging. In addition, the NW fabrication by template-assisted electrochemical deposition provides a versatile method with tight control over the NW properties. Especially iron NWs and iron-iron oxide (core-shell) NWs are suitable for biomedical applications, due to their high magnetization and low toxicity.
In this work, we provide a method to biofunctionalize iron/iron oxide NWs with specific antibodies directed against a specific cell surface marker that is overexpressed in a large number of cancer cells. Since the method utilizes the properties of the iron oxide surface, it is also applicable to superparamagnetic iron oxide nanoparticles. The NWs are first coated with 3-aminopropyl-tri-ethoxy-silane (APTES) acting as a linker, which the antibodies are covalently attached to. The APTES coating and the antibody biofunctionalization are proven by electron energy loss spectroscopy (EELS) and zeta potential measurements. In addition, the antigenicity of the antibodies on the NWs is tested by using immunoprecipitation and western blot. The specific targeting of the biofunctionalized NWs and their biocompatibility are studied by confocal microscopy and a cell viability assay.

In this work, we provide a protocol to biofunctionalize magnetic nanomaterials with antibodies for specific cell targeting. As examples, we utilize iron nanowires to target cancer cells.

Magnetic nanomaterials have received great attention in different biomedical applications. Biofunctionalizing these nanomaterials with specific targeting ...

Preparation and In Vitro Characterization of Magnetized miR-modified Endothelial Cells

To date, the available surgical and pharmacological treatments for cardiovascular diseases (CVD) are limited and often palliative. At the same time, gene and cell therapies are highly promising alternative approaches for CVD treatment. However, the broad clinical application of gene therapy is greatly limited by the lack of suitable gene delivery systems. The development of appropriate gene delivery vectors can provide a solution to current challenges in cell therapy. In particular, existing drawbacks, such as limited efficiency and low cell retention in the injured organ, could be overcome by appropriate cell engineering (i.e., genetic) prior to transplantation. The presented protocol describes the efficient and safe transient modification of endothelial cells using a polyethyleneimine superparamagnetic magnetic nanoparticle (PEI/MNP)-based delivery vector. Also, the algorithm and methods for cell characterization are defined. The successful intracellular delivery of microRNA (miR) into human umbilical vein endothelial cells (HUVECs) has been achieved without affecting cell viability, functionality, or intercellular communication. Moreover, this approach was proven to cause a strong functional effect in introduced exogenous miR. Importantly, the application of this MNP-based vector ensures cell magnetization, with accompanying possibilities of magnetic targeting and non-invasive MRI tracing. This may provide a basis for magnetically guided, genetically engineered cell therapeutics that can be monitored non-invasively with MRI.

Preparation and In Vitro Characterization of Magnetized miR-modified Endothelial Cells

This manuscript describes the efficient, non-viral delivery of miR to endothelial cells by a PEI/MNP vector and their magnetization. Thus, in addition to genetic modification, this approach allows for magnetic cell guidance and MRI detectability. The technique can be used to improve the characteristics of therapeutic cell products.

To date, the available surgical and pharmacological treatments for cardiovascular diseases (CVD) are limited and often palliative. At the same time, gene ...

Synthesis, Characterization, and Application of Superparamagnetic Iron Oxide Nanoprobes for Extrapulmonary Tuberculosis Detection

A molecular imaging probe comprising superparamagnetic iron oxide (SPIO) nanoparticles and Mycobacterium tuberculosis surface antibody (MtbsAb) was synthesized to enhance imaging sensitivity for extrapulmonary tuberculosis (ETB). An SPIO nanoprobe was synthesized and conjugated with MtbsAb. The purified SPIO-MtbsAb nanoprobe was characterized using TEM and NMR. To determine the targeting ability of the probe, SPIO-MtbsAb nanoprobes were incubated with Mtb for in vitro imaging assays and injected into Mtb-inoculated mice for in vivo investigation with magnetic resonance (MR). The contrast enhancement reduction on magnetic resonance imaging (MRI) of Mtb and THP1 cells showed proportional to the SPIO-MtbsAb nanoprobe concentration. After 30 min of intravenous SPIO-MtbsAb nanoprobe injection into Mtb-infected mice, the signal intensity of the granulomatous site was enhanced by 14-fold in the T2-weighted MR images compared with that in mice receiving PBS injection. The MtbsAb nanoprobes can be used as a novel modality for ETB detection.

To improve serological diagnostic tests for Mycobacterium tuberculosis antigens, we developed superparamagnetic iron oxide nanoprobes to detect extrapulmonary tuberculosis.

A molecular imaging probe comprising superparamagnetic iron oxide (SPIO) nanoparticles and Mycobacterium tuberculosis surface antibody (MtbsAb) was ...

Cell Labeling and Targeting with Superparamagnetic Iron Oxide Nanoparticles

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Chapters in this video

Registered Bioimaging of Nanomaterials for Diagnostic and Therapeutic Monitoring

Labeling Stem Cells with Ferumoxytol, an FDA-Approved Iron Oxide Nanoparticle

Labeling hESCs and hMSCs with Iron Oxide Nanoparticles for Non-Invasive in vivo Tracking with MR Imaging

Multimodal Imaging of Stem Cell Implantation in the Central Nervous System of Mice

Synthesis of Cationized Magnetoferritin for Ultra-fast Magnetization of Cells

Nanoparticle Delivery of an Oligonucleotide Payload in a Glioblastoma Multiforme Animal Model

Using Magnetometry to Monitor Cellular Incorporation and Subsequent Biodegradation of Chemically Synthetized Iron Oxide Nanoparticles

Biofunctionalization of Magnetic Nanomaterials

Preparation and In Vitro Characterization of Magnetized miR-modified Endothelial Cells

Synthesis, Characterization, and Application of Superparamagnetic Iron Oxide Nanoprobes for Extrapulmonary Tuberculosis Detection