LK は国立科学財団大学院研究フェローシップ ・ プログラム (DGE-1445197) とヴァンダービルト大学化学部門からの資金のために感謝しています。LK と EH オシリス TEM 装置 (NSF EPS 1004083) のための資金に感謝したいと思います。

1. Synthesis and Characterization of AVL
<ol>
	<li>Place a magnetic stir bar inside a 2 neck 500 mL round bottom flask (Flask 1) and seal with an appropriate sized rubber septum and steel wire. Flame dry the flask to remove moisture by purging with nitrogen gas connected through an inlet needle and open outlet needle in the septum, while using a butane flame torch to gently heat the outside of the flask by moving the flame along the surface.
	<ol>
		<li>Continue heating the entire flask by running the flame across the surface until moisture clouding the inside of the flask is not seen. Remove the flame and let the flask cool to room temperature while continuing the nitrogen flow throughout the reaction.</li>
	</ol>
	</li>
	<li>Add 156.25 mL anhydrous tetrahydrofuran (THF) via a 30 mL syringe to Flask 1. Cool Flask 1 to -78 &#176;C with a dry ice/acetone bath. Monitor the temperature with a thermometer throughout the reaction and add dry ice as needed to maintain -78 &#176;C. Begin stirring the magnetic stir bar using a magnetic stir plate to create a gentle vortex.</li>
	<li>Add N,N-diisopropylethylamine (DIPA) (3.30 mL, 2.3 x 10-2 mol) via a 5 mL syringe, followed by the dropwise addition of 2.5 M n-Butyllithium (9.34 mL, 2.3 x 10-2 mol) via a 10 mL glass syringe equipped with a needle locking mechanism and metal needle to Flask 1. Continue to stir using a magnetic stir plate for 15 min at -78 &#176;C.</li>
	<li>Flame dry (as described in step 1.1) and purge with argon gas (as described in step 1.1 with nitrogen gas) a 100 mL round bottom flask (Flask 2). Remove the argon gas inlet and outlet at the same time once the flask is cool enough to touch. Add 56 mL anhydrous THF via a 30 mL syringe and &#948;-valerolactone (VL) (1.97 mL, 2.1 x 10-2 mol) via a 5 mL syringe.</li>
	<li>Add the solution in Flask 2 to Flask 1 via a small cannula dropwise over 45 min while continuously stirring via a magnetic stir bar. Once Flask 2 is empty, remove the cannula and allow Flask 1 to continue stirring for 15 min at -78 &#176;C.</li>
	<li>Flame dry (as described in step 1.1) and purge with argon gas (as described in step 1.1 with nitrogen gas) a 25 mL round bottom flask (Flask 3). Remove the argon gas inlet and outlet at the same time once the flask is cool enough to touch, to maintain positive pressure inside the flask. Add ally bromide (2.02 mL, 2.3 x 10-2 mol) and hexamethyphosphoramide (HMPA) (4.43 mL, 2.5 x 10-2 mol) each via a 5 mL syringe.</li>
	<li>Add Flask 3 to Flask 1 via a small cannula dropwise. Once Flask 3 is empty, remove the cannula.
	<ol>
		<li>Remove as much dry ice and cold acetone as possible from the dry ice/acetone bath in which Flask 1 is submerged using a scoop and plastic cup. Replace with room temperature acetone to raise the bath to -40 &#176;C and allow Flask 1 to continue stirring for 2 h while monitoring the temperature. If the temperature increases above -40 &#176;C, add a few pieces of dry ice to cool the acetone.</li>
		<li>Warm to -10 &#176;C by removing the cold acetone and dry ice and replace with room temperature acetone.</li>
	</ol>
	</li>
	<li>Remove the septum from Flask 1 and quench the reaction with a 150 mL saturated ammonium chloride solution while stirring via a magnetic stir bar. Place Flask 1 in a freezer at -20 &#176;C overnight for storage.</li>
	<li>Remove Flask 1 from the freezer and allow to warm to room temperature. Pour the solution from Flask 1 into a 500 mL separatory funnel.</li>
	<li>Add 50 mL dichloromethane (DCM), cap the separatory funnel, and rock gently to mix the DCM and aqueous/THF mixture to extract the product into the organic layer. Collect the organic layer into a 500 mL beaker containing an appropriately sized magnetic stir bar by opening the separatory funnel stopcock and set aside. Repeat two times.</li>
	<li>Collect all the organics into the same beaker and stir over magnesium sulfate (to remove any residual water) using a magnetic stir plate until the magnesium sulfate no longer clumps when added to solution. Discard the aqueous waste.</li>
	<li>Remove the magnesium sulfate solid from the organic product solution by using a filter paper inside a glass funnel and collect the organics in a 250 mL round bottom flask. Rinse the filter paper and solid magnesium sulfate with excess DCM to ensure that all the product is collected.</li>
	<li>Remove the solvent from the product by rotary evaporation while heating at 30 &#176;C and using a water aspirator as the vacuum source.</li>
	<li>Purify the crude product by column chromatography10 using a silica gel as the stationary phase and eluting beginning with 3% ethyl acetate/hexanes for 1 column volume (CV), increasing the gradient to 29% ethyl acetate/hexanes over 5 CVs. Collect the fractions in 16 x 150 mm2 borosilicate glass tubes.</li>
	<li>Perform thin layer chromatography using 20% ethyl acetate/hexanes as eluent to determine the product fractions.</li>
	<li>Combine all product fractions into an appropriately sized round bottom flask and remove the solvent using rotary evaporation at 40 &#176;C. Transfer to a pre-weighed product vial and place under a high vacuum at 0.05 torr to obtain pure AVL. Characterize the product by 1H NMR11 (CDCl3, 400 MHz): &#948; 5.75 (m, 1H), 5.06 (m, 2H), 4.26 (m, 2H), 2.54 (m, 3H), 2.28 (m, 1H), 2.03 (m, 1H), 1.87 (m, 1H), 1.54 (m, 1H). Yield: 2.07 g (70.56%).</li>
</ol>
2. Synthesis and Characterization of VL- co- AVL
<ol>
	<li>Flame dry and purge with nitrogen gas a 25 mL round bottom flask equipped with a magnetic stir bar and septum.
	<ol>
		<li>Flame dry the flask to remove moisture by purging with nitrogen gas connected through an inlet needle and open outlet needle in the septum, while using a butane flame torch to gently heat the outside of the flask by moving the flame along the surface.</li>
		<li>Continue heating the entire flask by running the flame across the surface until moisture clouding the inside of the flask is not seen. Remove the flame and let the flask cool to room temperature while continuing the nitrogen flow throughout the reaction.</li>
	</ol>
	</li>
	<li>Quickly remove the septum from the round bottom and add tin(II) triflate (2.5 mg, 5.9&#160; x 10-6 mol) to the very bottom of the flask using a spatula. Replace the septum.</li>
	<li>Add 3-methyl-1-butanol (72.6 &#181;L, 6.6 x 10-3 mol) via a 100 &#181;L microsyringe and 1.33 mL anhydrous DCM via a 2 mL syringe sequentially. Stir via a magnetic stir plate for 10 min.</li>
	<li>Add AVL (0.48 mL, 3.7 x 10-3 mol) and VL (1.37 mL, 1.4 x 10-2 mol) sequentially via a syringe. Allow to continue stirring for 18 - 20 h. 
	NOTE: The AVL and VL percentage in the final copolymer can be altered by stoichiometry in this step.</li>
	<li>Quench the reaction by adding ~5 mL methanol (MeOH). Add ~100 mg solid-support tin scavenger and stir for 2 h. Filter by gravity filtration to remove the solid.</li>
	<li>Remove the solvent under rotary evaporation with a water aspirator as the vacuum source while heating at 30 &#176;C until the solution is viscous. Precipitate the solution dropwise into 500 mL cold MeOH (chilled with dry ice for at least 1 h) to produce flakes of white solid. Filter the solution by vacuum filtration into a funnel containing a fritted glass disc with filter paper to collect the solid. 
	NOTE: If precipitation produces a cloudy supernatant or fine powder which goes through the filter paper, then the product solution is too dilute. All supernatant solvent should be removed by rotary evaporation with a water aspirator as the vacuum source while heating at 30 &#176;C until the solution is viscous and then precipitation should be performed again.</li>
	<li>Transfer the solid product to a pre-weighed vial via a spatula and dry overnight via high vacuum pressure of 0.05 torr to collect the white, flaky solid.</li>
	<li>Characterize the polymer by 1H NMR11 (CDCl3, 400 MHz): &#948; 5.71 (m, 1H), 5.03 (t, 2H), 4.08 (m, 4H), 3.65 (t, 2H), 2.15 - 2.50 (m, 5H), 1.47-1.78 (m, 9H), 0.91 (d, 6H). 81.42% VL, 18.58% AVL, 2,940 g/mol, 578 g/mol repeat unit of AVL. Yield: 1.43 g, (73.43%).</li>
</ol>
3. Post-polymerization Epoxidation to Produce Epoxy-valerolactone (EVL) Copolymer Units
<ol>
	<li>Add VL-co-AVL copolymer (500 mg, 1.7&#160; x 10-4 mol, 2,940 g/mol) to a 6-dram vial with a magnetic stir bar. Add 6.15 mL anhydrous DCM to the vial and vortex to solubilize the polymer.</li>
	<li>Add meta-chloroperoxybenzoic acid (mCPBA) (74.53 mg, 4.3 x 10-4 mol) to a second 6-dram vial. Add 6.15 mL anhydrous DCM and vortex until the mCPBA is solubilized completely. 
	NOTE: The conversion ratio of allyls to epoxides can be varied by altering the stoichiometry in this step. The final allyl concentration in the solvent should be 0.065 M.</li>
	<li>Transfer the mCPBA solution to the VL-AVL solution. Cap the reaction and cover with a plastic paraffin film. Allow to stir for 48 h.</li>
	<li>Transfer the reaction mixture to a 50 mL separatory funnel. Add 15 mL saturated sodium bicarbonate, cap the separatory funnel, and rock gently to mix. Collect the organic layer containing the product into a 50 mL Erlenmeyer flask with an appropriate sized magnetic stir bar (product flask).
	<ol>
		<li>Add 5 mL DCM to the aqueous layer that is still in the separatory funnel, cap, and then rock gently. Collect the organics into the product flask. Discard the aqueous waste. Transfer the organic layer back into a separatory funnel. Repeat this aqueous wash two times.</li>
	</ol>
	</li>
	<li>Add magnesium sulfate (to remove any residual water) to the product flask while stirring over a magnetic stir plate. Continue adding small scoops of magnesium sulfate until it no longer clumps when added. Use a glass funnel fitted with a filter paper to remove the solid magnesium sulfate while transferring the mixture to a 50 mL round bottom flask.</li>
	<li>Remove the solvent by rotary evaporation with a water aspirator as the vacuum source and heating at 25 &#176;C. Transfer the contents of the round bottom flask to a pre-weighed product vial and remove the solvent by rotary evaporation. Place on high vacuum at 0.05 torr overnight to produce a white, waxy solid.</li>
	<li>Characterize by 1H NMR11 (CDCl3, 400 MHz): &#948; 5.71 (m, 1H), 5.03 (t, 2H), 4.08 (m, 4H), 3.65 (t, 2H), 2.94 (d, 1H), 2.90 (s, 1H), 2.74 (s, 1H), 2.15-2.50 (m, 5H), 1.47-1.78 (m, 9H), 0.92 (d, 6H). 84.53% VL, 9.65% AVL, 5.82% EVL, 2,855 g/mol, 1,841 g/mol repeat unit of EVL. Yield: 417.3 mg, (83.46%).</li>
</ol>
4. Nanosponge Synthesis and Characterization
<ol>
	<li>Dissolve the VL-co-AVL-co-EVL polymer (200 mg, 7.0 x 10-5 mol, 2,855 g/mol) in 20.01 mL anhydrous DCM for an epoxide concentration of 0.0054 M. Transfer to a 100 mL round bottom flask with a 14/20 neck. 
	NOTE: To catalyze the reaction, 100 &#181;L aqueous saturated sodium bicarbonate can be added in this step.</li>
	<li>Place the reaction flask in an oil bath at 50 &#176;C. Stir the solution with a fast vortex and add 2,2&#39;-(ethylenedioxy)bis(ethylamine) (21.45 &#181;L, 2.9 10-4 mol) via a microsyringe dropwise. Fit the neck of the flask with a water-jacketed condenser with cool water flowing through it, fitted with a 14/20 neck adapter, and reflux the solution for 12 h. Ensure a very tight seal between the neck of the flask and the condenser to avoid solvent evaporation.</li>
	<li>Remove excess solvent from the reaction flask by rotary evaporation at 25 &#176;C until a viscous solution is obtained.</li>
	<li>Place a large magnetic stir bar into a 2 L beaker. Cut an approximately six-inch section of 10 K molecular weight cut-off (MWCO) dialysis tubing and fold one end then close with a dialysis clip.
	<ol>
		<li>Transfer the product to 10 K MWCO dialysis tubing. Rinse the flask with excess DCM and transfer it to the tubing.Fold the top of the tubing and close with a dialysis clip that has a wire for hanging. Hang the dialysis tubing on the side of the beaker using the wire and fill the beaker with DCM until the dialysis tubing is completely submerged.</li>
		<li>Place on a magnetic stir plate and stir gently. Cover the beaker with aluminum foil to prevent solvent evaporation. Remove the solvent by pouring into a waste container and replace with fresh DCM three times daily for 48 h to remove the unreacted polymer and crosslinker.</li>
	</ol>
	</li>
	<li>Remove all solvent from the beaker and transfer the contents of the dialysis tubing to a 10 mL syringe fitted with a 0.45 &#181;m polytetrafluoroethylene (PTFE) syringe filter. Push the solution through the filter directly into a pre-weighed product vial to remove any remaining impurities. Remove the solvent by rotary evaporation at 25 &#176;C, then place on high vacuum at 0.05 torr overnight to collect the light yellow, waxy solid.</li>
	<li>Characterize by 1H NMR11 (CDCl3, 400 MHz): &#948; 5.71 (m, 1H), 5.03 (t, 2H), 4.08 (m, 4H), 3.60-3.67 (t, 14H), 2.94 (d, 1H), 2.90 (s, 1H), 2.74 (s, 1H), 2.15-2.50 (m, 5H), 1.47-1.78 (m, 9H), 0.92 (d, 6H). Yield: 176.9 mg (88.45%).</li>
</ol>
5. TEM Imaging of Nanosponge Morphology and Size
<ol>
	<li>Filter 5 mL cell culture water through a 0.2 &#181;m PTFE syringe filter.</li>
	<li>Place 0.5 mg nanosponges into a 1.5 mL centrifuge tube. Add 1 mL filtered cell culture water. Use a probe sonicator (20 kHz, 40 a) to sonicate the solution with 2 s bursts 4 - 5 times at room temperature until the particles have developed a fine suspension. Do not use prolonged sonication or let the solution heat up as this will cause aggregation.</li>
	<li>Add 30 mg phosphotungstic acid hydrate (PTA) to 1 mL filtered cell culture water in a 1.5 mL centrifuge tube. Vortex on the highest setting for 10 s or until the PTA is completely solubilized to produce 3% PTA solution.</li>
	<li>Use a 1 mL syringe with 22 G needle to draw up 0.5 mL 3% PTA solution. Add 4 drops of the 3% PTA solution to the particles and vortex on the highest setting for 10 s. Use a pair of self-closing tweezers to pick up a TEM grid then dip it into the particles solution quickly, three times. Let the grid dry for 5 h under a cover to reduce dust collection on the grid.</li>
	<li>Perform TEM imaging12 of the sample using high contrast and 40 &#181;m objective.</li>
</ol>

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再現可能なナノスポンジ サイズを取得は、薬物送達アプリケーションに不可欠です。重合とナノスポンジ合成における複数パラメーターは、結果として得られる粒子のサイズと架橋密度を影響します。3 つの重要なパラメーターは、我々 の分析で識別された: 架橋剤及びエポキシ樹脂ペンダント機能高分子の分子量。分子量とエポキシド ナノスポンジ合成機能の範囲を生成するために、VL-<em...

これらナノシステム1の薬物放出プロファイルをガイドに影響を与える非常に重要なは分子間架橋結合に基づくナノ粒子のサイズと架橋密度を正確にチューニングします。すなわち、設計ナノスポンジ無依存異なるネットワーク密度の粒子を準備、前駆体ポリマーのペンダント機能および組み込まれる親水性の架橋剤の同等物に頼っています。このアプローチで前駆体および架橋剤、溶媒中の濃度はバルク ゲルではなく、個々 のサイズの形ナノ粒子に重要です。定量核磁気共鳴分光法 (NMR) 評価技術を利用して法人ペンダント機能と高分子の分子量の正確な測定可能します。ナノ粒子を形成、一度集中し、ナノゲルの性格を持つことがなく有機物の可溶化できます。
ナノ粒子ドラッグデリバリーの最近の研究はポリの使用に焦点を当てて (乳酸-co-グリコール酸) (PLGA) 自己組織化ナノ粒子2,3,4,5,6。PLGA 薬物送達アプリケーションに適している分解性エステルの連携があり、しばしばそのステルス特性7のため poly(ethylene glycol) (PEG) と組み合わせています。ただし、さらに高機能化有機物で、PLGA 粒子形成の自己組織化の性質のため粒子を溶解できません。PLGA ナノ粒子とは対照的は、提案されたメソッドは、定義されたサイズと形態、オーガニックで不安定であり水溶液1が低下するナノ粒子を形成共有結合で架橋を提供します。このアプローチの利点は、さらに化学的にナノスポンジ8の表面を高機能化する能力と有機溶剤の安定性は医薬品化合物1,9で粒子の後読み込みを使用できます。この方法では、水溶液に沈殿物によって疎水性小分子のカプセル化を実現できます。一緒に親水性の短い架橋ポリエステルのバックボーンの疎水性はこれらの粒子に体温でアモルファス文字を与えます。さらに、薬物の読み込み後、粒子は容易に注射で体内に水溶液中における微細懸濁液を形成できます。これらのポリエステルの nanosponges の合成用パラメーターを評価し、デザイン、サイズおよび形態の調節に非常に重要であるものを決定するこの作業における私たちの目標です。

<table><tbody><tr><td>2,2&#039;-(Ethylenedioxy)bis(ethylamine)</td><td>Sigma-Aldrich</td><td>385506-100ML</td><td></td></tr><tr><td>3-methyl-1-butanol</td><td>Sigma-Aldrich</td><td>309435-100ML</td><td>anhydrous, &amp;ge;99%</td></tr><tr><td>Acetone</td><td>Sigma-Aldrich</td><td>179124-4L</td><td></td></tr><tr><td>Allyl bromide</td><td>Sigma-Aldrich</td><td>A29585-5G</td><td>&amp;ge;99%</td></tr><tr><td>Ammonium chloride</td><td>Fisher Scientific</td><td>A661-500</td><td>saturated solution in DI water</td></tr><tr><td>Cell culture water</td><td>Sigma-Aldrich</td><td>W3500-500ML</td><td>Filtered through 0.45 &amp;mu;m syringe filter</td></tr><tr><td>Dichloromethane (DCM)</td><td>Sigma-Aldrich</td><td>270997-100ML</td><td>anhydrous, &amp;ge;99%, contains 40 - 150 ppm amylene as stabilizer</td></tr><tr><td>Ethyl Acetate</td><td>Fisher Scientific</td><td>E145SK-4</td><td></td></tr><tr><td>EZFlow 0.2 &amp;mu;m Syringe Filter</td><td>Foxx Life Sciences</td><td>386-2116-OEM</td><td>Hydrophillic PTFE, 13 mm</td></tr><tr><td>EZFlow 0.45 &amp;mu;m Syringe Filter</td><td>Foxx Life Sciences</td><td>386-3126-OEM</td><td>Hydrophillic PTFE, 25 mm</td></tr><tr><td>Fisherbrand Disposable Borosilicate Glass Test Tubes with Plain End</td><td>Fisher Scientific</td><td>14-961-31</td><td></td></tr><tr><td>Fisherbrand Microcentrifuge Tubes</td><td>Fisher Scientific</td><td>14-666-318</td><td>1.5 mL</td></tr><tr><td>Hamilton Microliter Syringe, 100 &amp;mu;L</td><td>Hamilton Company</td><td>80600</td><td>Model 710 N SYR, Cemented NDL, 22s ga, 2 in, point style 2</td></tr><tr><td>Hexamethylphosphoramide</td><td>Sigma-Aldrich</td><td>H11602-100G</td><td>&amp;ge;99%, contains &amp;le;1,000 ppm propylene oxide as stabilizer</td></tr><tr><td>Hexanes</td><td>Fisher Scientific</td><td>H292-4</td><td></td></tr><tr><td>Magnesium sulfate anhydrous</td><td>Fisher Scientific</td><td>M65-500</td><td></td></tr><tr><td>Meta-chloroperoxybenzoic acid</td><td>Sigma-Aldrich</td><td>273031-100G</td><td>Purified to &amp;ge;99% by buffer wash</td></tr><tr><td>Methanol (MeOH)</td><td>Sigma-Aldrich</td><td>322415-100ML</td><td>anhydrous, &amp;ge;99%</td></tr><tr><td>N-butyllithium solution</td><td>Sigma-Aldrich</td><td>230707-100ML</td><td>2.5 M in hexanes</td></tr><tr><td>N,N-diisopropylethylamine</td><td>Sigma-Aldrich</td><td>550043-500ML</td><td>&amp;ge;99%</td></tr><tr><td>Parafilm M</td><td>Sigma-Aldrich</td><td>P7793-1EA</td><td></td></tr><tr><td>PELCO Pro Reverse (Self-Closing) Tweezers</td><td>Ted Pella, Inc.</td><td>5375-NM</td><td></td></tr><tr><td>Phosphotungstic acid hydrate</td><td>Alfa Aesar</td><td>40116</td><td></td></tr><tr><td>Q55 Sonicator</td><td>Qsonica</td><td>Q55-110</td><td>55 Watts, 20 kHz</td></tr><tr><td>SiliaMetS Cysteine</td><td>Silicycle</td><td>R80530B-10g</td><td></td></tr><tr><td>SnakeSkin Dialysis Clips</td><td>Thermo Scientific</td><td>68011</td><td></td></tr><tr><td>SnakeSkin Dialysis Tubing, 10K MWCO</td><td>Thermo Scientific</td><td>68100</td><td></td></tr><tr><td>Sodium bicarbonate</td><td>Fisher Scientific</td><td>5233-500</td><td>saturated solution in DI water</td></tr><tr><td>TEM grid</td><td>Ted Pella, Inc.</td><td>01822-F</td><td>Ultrathin Carbon Type-A, 400 mesh, Copper, approx. grid hole size: 42 &amp;micro;m</td></tr><tr><td>Tetrahydrofuran (THF)</td><td>Sigma-Aldrich</td><td>401757-1L</td><td>Anhydrous, &amp;ge;99.9%, inhibitor-free</td></tr><tr><td>Tin(II) trifluoromethanesulfonate</td><td>Sigma-Aldrich</td><td>388122-1G</td><td></td></tr><tr><td>Vortex-Genie 2</td><td>Scientific Industries</td><td>SI-0236</td><td></td></tr><tr><td>Whatman Filter Paper, Grade 1</td><td>Fisher Scientific</td><td>09-805H</td><td>Circles, 185 mm</td></tr><tr><td>&amp;delta;-valerolactone</td><td>Sigma-Aldrich</td><td>389579-100ML</td><td>Purified by vacuum distillation</td></tr></tbody></table>

nanosponge tunability in size and crosslinking density

ペンダント エポキシド機能と制御寸法ナノスポンジの混入を含む線形のポリエステルの合成のためのプロトコルについて述べる。このアプローチは、得られたポリマーのペンダント機能化へキーである機能性ラクトンの合成から始まります。バレロラクトン (VL) とアリル-バレロラクトン (AVL) は、開環重合に共が。ポストキュア変更、ペンダント アリル グループの一部またはすべてにエポキシ基をインストールする使用されます。希薄溶液中の高分子と低分子芳香族ジアミン架橋剤目的ナノスポンジ サイズと架橋密度に基づくフォーム ナノ粒子にエポキシ樹脂アミン化学を採用します。ナノスポンジ サイズは、寸法と分布を決定する透過電子顕微鏡 (TEM) イメージングによって特徴付けられます。このメソッドは、高度調整可能なポリエステルが可変性ナノ粒子、小分子薬のカプセル化のため使用することができますを作成することが経路を提供します。バックボーンの性質のため、これらの粒子は疎水性小分子の広い範囲の制御放出の加水分解や酵素によって分解。

ナノスポンジの合成パラメーターとその結果のサイズの関係を評価するには、各高分子前駆体の濃度とペンダントの機能は重要です。図 1で、12 h の DCM で両方前駆体高分子/ジアミン誘導体の架橋を組み込んだ後、その nanosponges の successfulsynthetic 方式が還流条件下で実施は。ソリューションのエポキシド濃度も離散的な粒子の形成に重要です。?...

Watch this Scientific Journal Video about Nanosponge Tunability in Size and Crosslinking Density at JoVE.com

Nanosponge Tunability in Size and Crosslinking Density

ペンダント機能を含む線形のポリエステルから共有架橋ナノ粒子のサイズと架橋密度を調整するためのプロセスについて説明します。合成パラメーター (ポリマーの分子量、ペンダント機能定款および架橋剤) を調整することによって薬物送達アプリケーションの必要なナノ粒子のサイズと架橋密度を実現できます。

サイズと架橋密度にナノスポンジ可変性

We describe a protocol for the synthesis of linear polyesters containing pendant epoxide functionality and their incorporation into a nanosponge with ...

nanosponge-tunability-in-size-and-crosslinking-density

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7.6K ビュー.  Vanderbilt University. ペンダント機能を含む線形のポリエステルから共有架橋ナノ粒子のサイズと架橋密度を調整するためのプロセスについて説明します。合成パラメーター (ポリマーの分子量、ペンダント機能定款および架橋剤) を調整することによって薬物送達アプリケーションの必要なナノ粒子のサイズと架橋密度を実現できます。

ビデオ: Nanosponge Tunability in Size and Crosslinking Density

Fabrication, Densification, and Replica Molding of 3D Carbon Nanotube Microstructures

The introduction of new materials and processes to microfabrication has, in large part, enabled many important advances in microsystems, lab-on-a-chip devices, and their applications. In particular, capabilities for cost-effective fabrication of polymer microstructures were transformed by the advent of soft lithography and other micromolding techniques 1, 2, and this led a revolution in applications of microfabrication to biomedical engineering and biology. Nevertheless, it remains challenging to fabricate microstructures with well-defined nanoscale surface textures, and to fabricate arbitrary 3D shapes at the micro-scale. Robustness of master molds and maintenance of shape integrity is especially important to achieve high fidelity replication of complex structures and preserving their nanoscale surface texture. The combination of hierarchical textures, and heterogeneous shapes, is a profound challenge to existing microfabrication methods that largely rely upon top-down etching using fixed mask templates. On the other hand, the bottom-up synthesis of nanostructures such as nanotubes and nanowires can offer new capabilities to microfabrication, in particular by taking advantage of the collective self-organization of nanostructures, and local control of their growth behavior with respect to microfabricated patterns. 
Our goal is to introduce vertically aligned carbon nanotubes (CNTs), which we refer to as CNT "forests", as a new microfabrication material. We present details of a suite of related methods recently developed by our group: fabrication of CNT forest microstructures by thermal CVD from lithographically patterned catalyst thin films; self-directed elastocapillary densification of CNT microstructures; and replica molding of polymer microstructures using CNT composite master molds. In particular, our work shows that self-directed capillary densification ("capillary forming"), which is performed by condensation of a solvent onto the substrate with CNT microstructures, significantly increases the packing density of CNTs. This process enables directed transformation of vertical CNT microstructures into straight, inclined, and twisted shapes, which have robust mechanical properties exceeding those of typical microfabrication polymers. This in turn enables formation of nanocomposite CNT master molds by capillary-driven infiltration of polymers. The replica structures exhibit the anisotropic nanoscale texture of the aligned CNTs, and can have walls with sub-micron thickness and aspect ratios exceeding 50:1. Integration of CNT microstructures in fabrication offers further opportunity to exploit the electrical and thermal properties of CNTs, and diverse capabilities for chemical and biochemical functionalization 3.

We present methods for fabrication of patterned microstructures of vertically aligned carbon nanotubes (CNTs), and their use as master molds for production of polymer microstructures with organized nanoscale surface texture. The CNT forests are densified by condensation of solvent onto the substrate, which significantly increases their packing density and enables self-directed formation of 3D shapes.

製造、ち密化、および3Dカーボンナノチューブの微細構造のレプリカ成形

The introduction of new materials and processes to microfabrication has, in large part, enabled many important advances in microsystems, lab-on-a-chip ...

工学

Functionalization of Single-walled Carbon Nanotubes with Thermo-reversible Block Copolymers and Characterization by Small-angle Neutron Scattering

We demonstrate a protocol for single-walled carbon nanotube functionalization using thermo-sensitive PEO-PPO-PEO triblock copolymers in an aqueous solution. In a carbon nanotube/PEO105-PPO70-PEO105 (poloxamer 407) aqueous solution, the amphiphilic poloxamer 407 adsorbs onto the carbon nanotube surfaces and self-assembles into continuous layers, driven by intermolecular interactions between constituent molecules. The addition of 5-methylsalicylic acid changes the self-assembled structure from spherical-micellar to a cylindrical morphology. The fabricated poloxamer 407/carbon nanotube hybrid particles exhibit thermo-responsive structural features so that the density and thickness of poloxamer 407 layers are also reversibly controllable by varying temperature. The detailed structural properties of the poloxamer 407/carbon nanotube particles in suspension can be characterized by small-angle neutron scattering experiments and model fit analyses. The distinct curve shapes of the scattering intensities depending on temperature control or addition of aromatic additives are well described by a modified core-shell cylinder model consisting of a carbon nanotube core cylinder, a hydrophobic shell, and a hydrated polymer layer. This method can provide a simple but efficient way for the fabrication and in-situ characterization of carbon nanotube-based nano particles with a structure-tunable encapsulation.

A method for the functionalization of carbon nanotubes with structure-tunable polymeric encapsulation layers and structural characterization using small-angle neutron scattering is presented.

小角中性子散乱による熱可逆性ブロック共重合体と特性を持つ単層カーボンナノチューブの機能化

We demonstrate a protocol for single-walled carbon nanotube functionalization using thermo-sensitive PEO-PPO-PEO triblock copolymers in an aqueous ...

化学

Creating Sub-50 Nm Nanofluidic Junctions in PDMS Microfluidic Chip via Self-Assembly Process of Colloidal Particles

Polydimethylsiloxane (PDMS) is the prevailing building material to make microfluidic devices due to its ease of molding and bonding as well as its transparency. Due to the softness of the PDMS material, however, it is challenging to use PDMS for building nanochannels. The channels tend to collapse easily during plasma bonding. In this paper, we present an evaporation-driven self-assembly method of silica colloidal nanoparticles to create nanofluidic junctions with sub-50 nm pores between two microchannels. The pore size as well as the surface charge of the nanofluidic junction is tunable simply by changing the colloidal silica bead size and surface functionalization outside of the assembled microfluidic device in a vial before the self-assembly process. Using the self-assembly of nanoparticles with a bead size of 300 nm, 500 nm, and 900 nm, it was possible to fabricate a porous membrane with a pore size of ~45 nm, ~75 nm and ~135 nm, respectively. Under electrical potential, this nanoporous membrane initiated ion concentration polarization (ICP) acting as a cation-selective membrane to concentrate DNA by ~1,700 times within 15 min. This non-lithographic nanofabrication process opens up a new opportunity to build a tunable nanofluidic junction for the study of nanoscale transport processes of ions and molecules inside a PDMS microfluidic chip.

We propose a simple self-assembly technique of silica colloidal nanoparticles to create a nanofluidic junction between two microchannels in polydimethylsiloxane (PDMS). Using this technique, a nanoporous bead membrane with a pore size down to ~45 nm was built inside a microchannel and applied to electrokinetic preconcentration of DNA samples.

コロイド粒子の自己組織化プロセスを介して、PDMSマイクロ流体チップ内のサブ50 Nmのナノ流体ジャンクショ​​ンを作成します

Polydimethylsiloxane (PDMS) is the prevailing building material to make microfluidic devices due to its ease of molding and bonding as well as its ...

Self-reporting Scaffolds for 3-Dimensional Cell Culture

Culturing cells in 3D on appropriate scaffolds is thought to better mimic the in vivo microenvironment and increase cell-cell interactions. The resulting 3D cellular construct can often be more relevant to studying the molecular events and cell-cell interactions than similar experiments studied in 2D. To create effective 3D cultures with high cell viability throughout the scaffold the culture conditions such as oxygen and pH need to be carefully controlled as gradients in analyte concentration can exist throughout the 3D construct. Here we describe the methods of preparing biocompatible pH responsive sol-gel nanosensors and their incorporation into poly(lactic-co-glycolic acid) (PLGA) electrospun scaffolds along with their subsequent preparation for the culture of mammalian cells. The pH responsive scaffolds can be used as tools to determine microenvironmental pH within a 3D cellular construct. Furthermore, we detail the delivery of pH responsive nanosensors to the intracellular environment of mammalian cells whose growth was supported by electrospun PLGA scaffolds. The cytoplasmic location of the pH responsive nanosensors can be utilized to monitor intracellular pH (pHi) during ongoing experimentation.

Biocompatible pH responsive sol-gel nanosensors can be incorporated into poly(lactic-co-glycolic acid) (PLGA) electrospun scaffolds. The produced self-reporting scaffolds can be used for in&#160;situ monitoring of microenvironmental conditions whilst culturing cells upon the scaffold. This is beneficial as the 3D cellular construct can be monitored in real-time without disturbing the experiment.

3次元細胞培養のための自己申告足場

Culturing cells in 3D on appropriate scaffolds is thought to better mimic the in vivo microenvironment and increase cell-cell interactions. The resulting ...

生物工学

Grafting Multiwalled Carbon Nanotubes with Polystyrene to Enable Self-Assembly and Anisotropic Patchiness

We demonstrate a straightforward protocol to graft pristine multiwalled carbon nanotubes (MWCNTs) with polystyrene (PS) chains at the sidewalls through a free-radical polymerization strategy to enable the modulation of the nanotube surface properties and produce supramolecular self-assembly of the nanostructures. First, a selective hydroxylation of the pristine nanotubes through a biphasic catalytically mediated oxidation reaction creates superficially distributed reactive sites at the sidewalls. The latter reactive sites are subsequently modified with methacrylic moieties using a silylated methacrylic precursor to create polymerizable sites. Those polymerizable groups can address further polymerization of styrene to produce a hybrid nanomaterial containing PS chains grafted to the nanotube sidewalls. The polymer-graft content, amount of silylated methacrylic moieties introduced and hydroxylation modification of the nanotubes are identified and quantified by Thermogravimetric Analysis (TGA). The presence of reactive functional groups hydroxyl and silylated methacrylate are confirmed by Fourier Transform Infrared Spectroscopy (FT-IR). Polystyrene-grafted carbon nanotube solutions in tetrahydrofuran (THF) provide wall-to-wall collinearly self-assembled nanotubes when cast samples are analyzed by transmission electron microscopy (TEM). Those self-assemblies are not obtained when suitable blanks are similarly cast from analogous solutions containing non-grafted counterparts. Therefore, this method enables the modification of the nanotube anisotropic patchiness at the sidewalls which results into spontaneous auto-organization at the nanoscale.

A procedure for the synthesis of polystyrene-grafted multiwalled carbon nanotubes using successive chemical modification steps to selectively introduce the polymer chains to the sidewalls and their self-assembly via anisotropic patchiness is presented.

ポリスチレン自己組織を有効にして異方的不均一性と多層カーボンナノ チューブを移植

We demonstrate a straightforward protocol to graft pristine multiwalled carbon nanotubes (MWCNTs) with polystyrene (PS) chains at the sidewalls through a ...

Multiscale Structures Aggregated by Imprinted Nanofibers for Functional Surfaces

Multiscale surface structures have attracted increasing interest owing to several potential applications in surface devices. However, an existing challenge in the field is the fabrication of hybrid micro-nano structures using a facile, cost-effective, and high-throughput method. To overcome these challenges, this paper proposes a protocol to fabricate multiscale structures using only an imprint process with an anodic aluminum oxide (AAO) filter and an evaporative self-aggregation process of nanofibers. Unlike previous attempts that have aimed to straighten nanofibers, we demonstrate a unique fabrication method for multiscale aggregated nanofibers with high aspect ratios. Furthermore, the surface morphology and wettability of these structures on various liquids were investigated to facilitate their use in multifunctional surfaces.

Presented is an easy method to fabricate nano-micro multiscale structures, for functional surfaces, by aggregating nanofibers fabricated using an anodic aluminum oxide filter.

マルチ スケール構造機能表面の刻印ナノファイバーによる集計

Multiscale surface structures have attracted increasing interest owing to several potential applications in surface devices. However, an existing ...

Fabricating Degradable Thermoresponsive Hydrogels on Multiple Length Scales via Reactive Extrusion, Microfluidics, Self-assembly, and Electrospinning

While various smart materials have been explored for a variety of biomedical applications (e.g., drug delivery, tissue engineering, bioimaging, etc.), their ultimate clinical use has been hampered by the lack of biologically-relevant degradation observed for most smart materials. This is particularly true for temperature-responsive hydrogels, which are almost uniformly based on polymers that are functionally non-degradable (e.g., poly(N-isopropylacrylamide) (PNIPAM) or poly(oligoethylene glycol methacrylate) (POEGMA)). As such, to effectively translate the potential of thermoresponsive hydrogels to the challenges of remote-controlled or metabolism-regulated drug delivery, cell scaffolds with tunable cell-material interactions, theranostic materials with the potential for both imaging and drug delivery, and other such applications, a method is required to render the hydrogels (if not fully degradable) at least capable of renal clearance following the required lifetime of the material. To that end, this protocol describes the preparation of hydrolytically-degradable hydrazone-crosslinked hydrogels on multiple length scales based on the reaction between hydrazide and aldehyde-functionalized PNIPAM or POEGMA oligomers with molecular weights below the renal filtration limit. Specifically, methods to fabricate degradable thermoresponsive bulk hydrogels (using a double barrel syringe technique), hydrogel particles (on both the microscale through the use of a microfluidics platform facilitating simultaneous mixing and emulsification of the precursor polymers and the nanoscale through the use of a thermally-driven self-assembly and cross-linking method), and hydrogel nanofibers (using a reactive electrospinning strategy) are described. In each case, hydrogels with temperature-responsive properties similar to those achieved via conventional free radical cross-linking processes can be achieved, but the hydrazone cross-linked network can be degraded over time to re-form the oligomeric precursor polymers and enable clearance. As such, we anticipate these methods (which may be generically applied to any synthetic water-soluble polymer, not just smart materials) will enable easier translation of synthetic smart materials to clinical applications.

Protocols are described for the fabrication of degradable thermoresponsive hydrogels based on hydrazone cross-linking of polymeric oligomers on the bulk scale, microscale, and nanoscale, the latter for preparation of both gel nanoparticles and nanofibers.

自己組織化反応押出、マイクロフルイディクス, 経由で複数の長さスケールでの分解性感温ハイドロゲルを加工・ エレクトロスピニング

While various smart materials have been explored for a variety of biomedical applications (e.g., drug delivery, tissue engineering, bioimaging, etc.), ...

Expanding Nanopatterned Substrates Using Stitch Technique for Nanotopographical Modulation of Cell Behavior

Substrate nanotopography has been shown to be a potent modulator of cell phenotype and function. To dissect nanotopography modulation of cell behavior, a large area of nanopatterned substrate is desirable so that enough cells can be cultured on the nanotopography for subsequent biochemical and molecular biology analyses. However, current nanofabrication techniques have limitations to generate highly defined nanopatterns over a large area. Herein, we present a method to expand nanopatterned substrates from a small, highly defined nanopattern to a large area using stitch technique. The method combines multiple techniques, involving soft lithography to replicate poly(dimethylsiloxane) (PDMS) molds from a well-defined mold, stitch technique to assemble multiple PDMS molds to a single large mold, and nanoimprinting to generate a master mold on polystyrene (PS) substrates. With the PS master mold, we produce PDMS working substrates and demonstrate nanotopographical modulation of cell spreading. This method provides a simple, affordable yet versatile avenue to generate well-defined nanopatterns over large areas, and is potentially extended to create micro-/nanoscale devices with hybrid components.

A protocol for producing a large area of nanopatterned substrate from small nanopatterned molds for study of nanotopographical modulation of cell behavior is presented.

細胞の挙動のNanotopographical変調のステッチ法を用いたナノパターン基板を拡大

Substrate nanotopography has been shown to be a potent modulator of cell phenotype and function. To dissect nanotopography modulation of cell behavior, a ...

DNA Nanotubes as a Versatile Tool to Study Semiflexible Polymers

Mechanical properties of complex, polymer-based soft matter, such as cells or biopolymer networks, can be understood in neither the classical frame of flexible polymers nor of rigid rods. Underlying filaments remain outstretched due to their non-vanishing backbone stiffness, which is quantified via the persistence length (lp), but they are also subject to strong thermal fluctuations. Their finite bending stiffness leads to unique, non-trivial collective mechanics of bulk networks, enabling the formation of stable scaffolds at low volume fractions while providing large mesh sizes. This underlying principle is prevalent in nature (e.g., in cells or tissues), minimizing the high molecular content and thereby facilitating diffusive or active transport. Due to their biological implications and potential technological applications in biocompatible hydrogels, semiflexible polymers have been subject to considerable study. However, comprehensible investigations remained challenging since they relied on natural polymers, such as actin filaments, which are not freely tunable. Despite these limitations and due to the lack of synthetic, mechanically tunable, and semiflexible polymers, actin filaments were established as the common model system. A major limitation is that the central quantity lp cannot be freely tuned to study its impact on macroscopic bulk structures. This limitation was resolved by employing structurally programmable DNA nanotubes, enabling controlled alteration of the filament stiffness. They are formed through tile-based designs, where a discrete set of partially complementary strands hybridize in a ring structure with a discrete circumference. These rings feature sticky ends, enabling the effective polymerization into filaments several microns in length, and display similar polymerization kinetics as natural biopolymers. Due to their programmable mechanics, these tubes are versatile, novel tools to study the impact of lp on the single-molecule as well as the bulk scale. In contrast to actin filaments, they remain stable over weeks, without notable degeneration, and their handling is comparably straightforward.

Semiflexible polymers display unique mechanical properties that are extensively applied by living systems. However, systematic studies on biopolymers are limited since properties such as polymer rigidity are inaccessible. This manuscript describes how this limitation is circumvented by programmable DNA nanotubes, enabling experimental studies on the impact of filament rigidity.

セミフレキシブル高分子を研究する多目的ツールとして DNA ナノチューブ

Mechanical properties of complex, polymer-based soft matter, such as cells or biopolymer networks, can be understood in neither the classical frame of ...

Synthesis of Stimuli-responsive Nanogels using Aqueous One-step Crosslinking and Co-nanopolymerization

Nanogels consisting of crosslinked-polymeric nanoparticles have been developed for the delivery of numerous chemical and biological therapeutics, owing to their versatile bottom-up synthesis and biocompatibility. While various methods have been employed for nanogel synthesis to date, very few have achieved it without the use of harsh organic solvents or high temperatures that can damage the integrity of the biological payload. In contrast, the methodology presented here accomplishes the synthesis of sub-100 nm sized, protein-loaded nanogels using mild reaction conditions. Here, we present a method for the non-covalent encapsulation of protein-based payloads within nano-gels that were synthesized using an aqueous-based, single-step, crosslinking copolymerization technique. In this technique, we initially electrostatically bind a protein-based payload to a cationic quaternary ammonium monomer and simultaneously cross-link and co-polymerize it using ammonium persulfate and N,N,N&#39;,N&#39;-tetramethylethylenediamine to form nanogels that entrap the protein payload. The size and polydispersity index of the nanogels is determined using dynamic light scattering (DLS), while the surface morphology is assessed by transmission electron microscopy (TEM). The mass of protein entrapped within nanogels is determined by calculating the encapsulation efficiency. Furthermore, the controlled-release ability of the nanogels via the gradual degradation of redox-responsive structural elements is also assessed in bioreduction assays. We provide examples of nanoparticle optimization data to demonstrate all caveats of nanogel synthesis and characterization using this technique. In general, uniformly sized nanogels were obtained with an average size of 57 nm and a polydispersity index value of 0.093. A high encapsulation efficiency of 76% was achieved. Furthermore, the nanogels exhibited controlled release of up to 86% of the encapsulated protein by gradual degradation of novel redox-responsive components in the presence of glutathione over 48 h.

Nanogels are an excellent and versatile nanoparticle platform for the delivery of biologics. Stimuli-responsive poly(ethylene) glycol-based polymeric nano-gels, capable of encapsulating protein-based payloads, were synthesized using a one-step cross-linking co-nanopolymerization strategy in aqueous conditions. The optimal fabrication and characterization of these novel nanoparticles are presented here.

水性ワンステップ架橋法とコナノ重合法による刺激応答性ナノゲルの合成

Nanogels consisting of crosslinked-polymeric nanoparticles have been developed for the delivery of numerous chemical and biological therapeutics, owing to ...

サイズと架橋密度にナノスポンジ可変性

要約

さらに動画を探す

製造、ち密化、および3Dカーボンナノチューブの微細構造のレプリカ成形

小角中性子散乱による熱可逆性ブロック共重合体と特性を持つ単層カーボンナノチューブの機能化

コロイド粒子の自己組織化プロセスを介して、PDMSマイクロ流体チップ内のサブ50 Nmのナノ流体ジャンクションを作成します

3次元細胞培養のための自己申告足場

ポリスチレン自己組織を有効にして異方的不均一性と多層カーボンナノチューブを移植

マルチスケール構造機能表面の刻印ナノファイバーによる集計

自己組織化反応押出、マイクロフルイディクス, 経由で複数の長さスケールでの分解性感温ハイドロゲルを加工・エレクトロスピニング

細胞の挙動のNanotopographical変調のステッチ法を用いたナノパターン基板を拡大

セミフレキシブル高分子を研究する多目的ツールとして DNA ナノチューブ

水性ワンステップ架橋法とコナノ重合法による刺激応答性ナノゲルの合成

サイズと架橋密度にナノスポンジ可変性

要約

さらに動画を探す

製造、ち密化、および3Dカーボンナノチューブの微細構造のレプリカ成形

小角中性子散乱による熱可逆性ブロック共重合体と特性を持つ単層カーボンナノチューブの機能化

コロイド粒子の自己組織化プロセスを介して、PDMSマイクロ流体チップ内のサブ50 Nmのナノ流体ジャンクショ​​ンを作成します

3次元細胞培養のための自己申告足場

ポリスチレン自己組織を有効にして異方的不均一性と多層カーボンナノ チューブを移植

マルチ スケール構造機能表面の刻印ナノファイバーによる集計

自己組織化反応押出、マイクロフルイディクス, 経由で複数の長さスケールでの分解性感温ハイドロゲルを加工・ エレクトロスピニング

細胞の挙動のNanotopographical変調のステッチ法を用いたナノパターン基板を拡大

セミフレキシブル高分子を研究する多目的ツールとして DNA ナノチューブ

水性ワンステップ架橋法とコナノ重合法による刺激応答性ナノゲルの合成

コロイド粒子の自己組織化プロセスを介して、PDMSマイクロ流体チップ内のサブ50 Nmのナノ流体ジャンクションを作成します

ポリスチレン自己組織を有効にして異方的不均一性と多層カーボンナノチューブを移植

マルチスケール構造機能表面の刻印ナノファイバーによる集計

自己組織化反応押出、マイクロフルイディクス, 経由で複数の長さスケールでの分解性感温ハイドロゲルを加工・エレクトロスピニング