この研究は、中国国立自然科学財団(81601608)とNUPTSF(NY216024)によって支援されました。

すべての動物実験は、動物のケアと実験動物の使用のためのOG製薬ガイドラインによって承認されたプロトコルに従って行われました。プロトコルは、OG製薬の実験動物のための倫理委員会のガイドラインに従いました。
ナノ粒子シェルドマイクロバブル(NSM)合成
<ol><li>脱イオン水に磁性ナノ粒子(Fe3O4、酸化鉄)を分散し、10mg/mLストック溶液を形成する。</li>
	<li>IONPs溶液を含むチューブを超音波洗浄機に20分間置きます。使用前に均一に分散したIONPsソリューションを入手してください。</li>
	<li>150 μLの脱イオン水、10 mMのドデシル硫酸ナトリウム(SDS)150 μL、ステップ1.1からイオンプスのストック溶液400 μLを加えます。1.5 mL遠心分離管で。</li>
	<li>ホモジナイザーを氷浴で足場で固定します。</li>
	<li>混合物のチューブを氷浴に入れ、ホモジナイザープローブを正確に配置して混合物溶液に浸す。</li>
	<li>ホモジナイザーの速度を20,000 rpmに調整し、ホモジナイザーを3分間オンにします。</li>
	<li>ホモジナイザーをオフにし、氷浴からチューブを取り外します。</li>
	<li>チューブをチューブラックに置き、室温で12時間安定させます。</li>
	<li>結果のNSMを磁石でチューブ壁に吸着し、上清を取り除きます。その後、1mLの新鮮な脱イオン水を補給します。</li>
	<li>洗浄プロセスを3回繰り返し、1mLの新鮮な蒸留水でNSMを再中断します。</li>
	<li>わずかに揺れた後、10 μLのNSMサスペンションをクリーンガラススライドに移します。</li>
	<li>20倍の倍率で蛍光顕微鏡を使用して、NSMの形態を可視化します。ランダムな領域で写真を撮ることを確認します。</li>
	<li>オープンアクセスナノ測定器1.2ソフトウェアを使用して、写真からNSMの直径を測定します。少なくとも200個のマイクロバブルを数えます。<ol>
<li>[ファイル] と [開く] をクリックして、処理するイメージ ファイルを選択します。イメージがインポートされたら、"定規" を押します。定規と同じ長さの赤い線を描きます。</li>
		<li>次に"設定"を押|「ルーラー」をクリックし、ルーラーの長さを入力します。イメージ内の個々のマイクロバブルの直径と同じ長さの線を描きます。すべての測定を完了し、「レポート」をクリックして| レポートを表示".</li>
	</ol>
</li>
</ol>2. NSMの音響応答
<ol><li>800 μL脱イオン水で200 μLのNSMを希釈し、1.5 mL遠心管に移してストック液を形成します。</li>
	<li>ファンクションジェネレータ、アンプ、インピーダンスマッチング、自家製のフォーカス変換器を接続します。トランスデューサを人工立方体シンクの底部の中央に置き、ハイドロフォンをオシロスコープに接続して出力超音波強度を監視します(図1)。脱イオン水をシンクに加え、トランスデューサを浸します。</li>
	<li>関数発生器をスイープモードに調整し、周波数範囲を10 kHzから900 kHzに調整し、振幅を20 Vpp(電圧ピークピーク)に設定します。アンプで0.1%に超音波のパワーを調整します。各サイクルの期間は 4 秒で、時間間隔は 1 秒です。</li>
	<li>チューブに1 mL NSMストック溶液サンプルを準備し、自家製の焦点を合わせたトランスデューサーの上に足場でチューブを固定します。マグネットをチューブの底に取り付け、NSMを引き付けます。</li>
	<li>ファンクション・ジェネレータとアンプの電源を入れます。超音波の5サイクル(25 s)の適用後に機能発生器をオフにします。磁石を取り外し、リリースされたIONPsを含む溶液の1mLを回収します。遠心管に1mLの脱イオン水を加えます。</li>
	<li>ステップ 2.5 を繰り返します。チューブ内のNSMが完全に崩壊するまで。</li>
	<li>前述の13のように、誘導結合プラズマ光発光分析(ICP-OES)によって放出されたすべてのIONPを定量化する。</li>
</ol>3. NSMの光応答
注:本研究では、808nmレーザーパワーと、Xuらによって以前に説明された赤外線熱画像カメラを含むレーザーシステムが20を利用される。
<ol><li>レーザーシステムの準備<ol>
<li>レーザーの電源をオンにし、数分間温めます。レトルトスタンドにファイバ結合808 nmレーザーダイオードを固定します。</li>
		<li>レーザー光を光ファイバーを通してサンプルステージに向け、サンプルステージに焦点を当て、凸レンズで6mmの光スポット(直径)を達成します。</li>
		<li>レーザーパワーメーターで出力出力を測定し、1 W/cm2に電力を調整します。</li>
		<li>三脚の赤外線熱画像カメラを固定します。カメラの電源を入れ、動作しているかどうかを確認します(例えば、関心のある領域(ROI)温度を監視します)。電源と赤外線熱画像カメラをオフにします。</li>
	</ol></li>
	<li>水溶液中の光熱測定<ol>
<li>1 mL サンプルを IONPs 濃度(1.05 mg/mL、1.35 mg/mL、3.65 mg/mL、5 mg/mL)で1.5 mL遠心分離チューブに調製します。</li>
		<li>目的のチューブをレーザー光の焦点領域に配置し、サンプルのベースライン温度を記録します。</li>
		<li>レーザーパワーと赤外線熱画像カメラをオンにし、サンプルを10分間連続して照射します。同時に、リアルタイムで温度を記録します。</li>
		<li>照射の10分後にレーザー電源と赤外線熱画像カメラをオフにします。リージョンの温度がベースラインに戻るのを待ちます。</li>
		<li>他のサンプルの測定のために 3.2.2 から 3.2.4 を繰り返します。 メモ:光熱測定の制御として、20°Cの脱イオン水を使用してください。</li>
	</ol></li>
	<li>培養細胞における光熱測定 注:マウス乳癌細胞(4T1)を光熱処理による阻害効果を調査するモデルとして選択した。<ol>
<li>ロズウェルパークメモリアルインスティテュート-1640(RPMI-1640)培地で細胞を供給し、10%胎児ウシ血清(FBS)と1%ペニシリンを添加します。培養環境を37°C、5%CO2に設定します。</li>
		<li>培養4T1細胞はT25フラスコで、90%合流に達すると細胞を1:2の割合で通過させる。 注: サブカルチャー比は、異なるラボの特定の細胞条件に応じて調整できます。</li>
		<li>培養液を取り出し、廃棄します。細胞層を1xPBS溶液でリンスし、トリプシン阻害剤を含む残存血清を除去する。</li>
		<li>剥離のためにフラスコにトリプシン-EDTA溶液(0.25%)の2 mLを加えます。その後、1640培地の3mLを加え、穏やかにピペットで細胞を吸引します。</li>
		<li>5mLの細胞懸濁液と遠心分離機を 500xg で3分間回収します。</li>
		<li>上清を取り除き、1mLの新鮮な1640培地を加え、細胞懸濁液を形成する。</li>
		<li>1mLの培養培地を含む共焦点皿に細胞懸濁液100μLを加える。細胞懸濁液の濃度が9 x 105/mLであり、細胞培養コンフォーカルディッシュの最終的な細胞濃度が8.1 x 104/mLであることを確認してください。</li>
		<li>接種細胞培養コンフォーカル皿をインキュベーターに24時間置きます。</li>
		<li>IONPsサンプルの異なる濃度(1.05mg/mL、1.35 mg/mL、3.65 mg/mL、5 mg/mL)を希釈し、1 mL溶液を無血清1640培地で作ります。</li>
		<li>コンフォーカル皿から培養液を吸引し、調製したサンプル溶液を添加する。</li>
		<li>レーザー電源をオンにします。皿の中央にレーザー光を集中させ、出力電力を1 W/cm2に調整します。赤外線熱画像カメラをオンにし、コンフォーカルディッシュ内の細胞を連続して10分間照射します。焦点を合わせる領域の温度をリアルタイムで記録します。</li>
		<li>レーザーカメラと赤外線熱画像カメラをオフにします。照射した皿をインキュベーターにさらに24時間移します。</li>
		<li>培養液を取り出して捨て、共焦点皿に1mLの新鮮な培養培地を加える。カルセイン-AM溶液(1 mg/mL)を5μL加えます。</li>
		<li>共焦点皿を37°C、5%CO2で15分間インキュベートします。細胞層を1倍のPBS溶液で2回リンスする。</li>
		<li>励起波長488nm、発光波長500~540nmの共焦点蛍光顕微鏡で細胞を観察・画像化します。</li>
		<li>共焦点画像の5つの領域をランダムに選択し、各領域の4T1細胞の数を手動でカウントします。すべての実験群の生細胞数を対照群と比較することにより、4T1細胞の生存率を定量化する。 注:20 °Cの無血清1640培地を光熱測定の制御として使用してください。細胞生存率制御群としてレーザー照射を行わずに試料を使用する。</li>
	</ol></li>
	<li>生体内での光熱測定<ol>
<li>平均体重25±2gの8週齢のICR雄マウスの3匹を準備する。</li>
		<li>20mLの脱イオン水にゼラチン粉末2gを加えます。溶液を40~50°Cに加熱し、ゼラチンゲルを完全に溶解し、透明で透明な溶液を形成する。</li>
		<li>3.4.2から溶液に100mgのIONPを追加します。</li>
		<li>ゲルを40~50°Cに加熱し、すぐに500μLのゼラチン溶液をマウスの右乳房パッドに注入します。</li>
		<li>レーザーパワーをオンにし、対象領域(マウスの右胸パッド)にレーザー光線を集中させる。出力電力を1 W/cm2に調整します。 赤外線熱画像カメラをオンにし、10分間連続して関心領域を照射します。関心領域の温度をリアルタイムで記録します。</li>
		<li>レーザーカメラと赤外線熱画像カメラをオフにします。</li>
		<li>CO2窒息および頸椎脱臼または研究所の動物研究委員会によって承認された任意の方法によってマウスを安楽死させる。</li>
	</ol></li>
</ol>4. 磁気温熱測定
注:ここでは、Wuらによって以前に記述された磁気温熱システムが利用されている(21) .
<ol><li>磁気高熱システムの準備には、交流磁場(AFM)発電機と赤外線熱画像カメラが含まれます。<ol>
<li>10分間チラーをオンにし、適度な無線周波数加熱機(AFM発電機)の電源を入れます。</li>
		<li>周波数(f)=415 kHz、磁場強度=1.8kA/mのパラメータを設定します。</li>
	</ol>
</li>
	<li>水溶液中の磁気高熱測定<ol>
<li>1.5 mL遠心分離管に異なるIONP濃度(1.05mg/mL、1.35 mg/mL、3.65 mg/mL、5 mg/mL)でサンプル1 mLを調製します。</li>
		<li>チューブを水冷磁気誘導銅コイルの中央に配置します。</li>
		<li>交流磁場(AFM)と赤外線熱画像カメラをオンにします。サンプルを連続して10分間誘導し、リアルタイムで温度を記録します。 注: カメラはサンプルの上部にあり、サンプルの断面図を提供します。</li>
		<li>AFM と赤外線熱画像カメラをオフにします。銅コイルの温度がベースラインに戻ってくるのを10分間待ちます。 注:高温に注意し、手との直接接触を避け、サンプルを取り外す前に冷却を待ちます。</li>
		<li>他のサンプルの測定のために 4.2.2 から 4.2.4 を繰り返します。</li>
		<li>適度な無線周波数加熱機(AFM)と冷却機の電源を切ります。 注:磁気温熱測定の制御として、20°Cの脱イオン水を使用してください。</li>
	</ol>
</li>
	<li>生体内での磁気温熱測定<ol>
<li>平均体重25±2gの8週齢のICR雄マウスの3匹を準備する。</li>
		<li>5 mg/mL IONPs溶液を含む10%ゼラチンゲル20 mLを調製します。</li>
		<li>ゼラチンゲルを40~50°Cに加熱し、すぐに500μLのゼラチン溶液を動物の右乳房パッドに注入します。 注:磁気誘発過熱実験は、インビトロ試験と同じパラメータを使用して加熱機で行われました。</li>
		<li>交流磁場(AFM)と赤外線熱画像カメラをオンにします。マウスの右胸パッドを水冷磁気誘導銅コイルの中央に置きます。</li>
		<li>赤外線熱画像カメラをオンにし、目的領域(マウスの右胸パッド)を10分間連続的に画像化し、対象領域の温度をリアルタイムで記録する。</li>
		<li>誘導の10分後に、マシンと赤外線熱画像カメラの電源スイッチをオフにします。銅コイルの温度がベースラインに10分間戻るのを待ちます。</li>
		<li>他のサンプルの測定のために 4.3.4 から 4.3.6 まで繰り返します。</li>
		<li>適度な無線周波数加熱機(AFM)と冷却機の電源を切ります。 注:高温に注意し、手との直接接触を避け、サンプルを取り外す前に冷却を待ちます。</li>
		<li>CO2窒息および頸椎脱臼または研究所の動物研究委員会によって承認された任意の方法によってマウスを安楽死させる。</li>
	</ol>
</li>
</ol>

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K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nanoparticles-based+magnetic+and+photo+induced+hyperthermia+for+cancer+treatment.">Nanoparticles-based magnetic and photo induced hyperthermia for cancer treatment.</a> Nano Today. 29, 100795 (2019).</li><li>Das, R., Rinaldi-Montes, N. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Boosted+Hyperthermia+Therapy+by+Combined+AC+Magnetic+and+Photothermal+Exposures+in+Ag/Fe3O4+Nanoflowers.">Boosted Hyperthermia Therapy by Combined AC Magnetic and Photothermal Exposures in Ag/Fe3O4 Nanoflowers.</a> ACS Applied Materials &amp; Interfaces. 8 (38), 25162-25169 (2016).</li><li>Yang, Y., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=1D+Coordination+Polymer+Nanofibers+for+Low-Temperature+Photothermal+Therapy.">1D Coordination Polymer Nanofibers for Low-Temperature Photothermal Therapy.</a> Advanced Materials. 29 (40), 1703588 (2017).</li><li>Curcio, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Iron+Oxide+Nanoflowers+CuS+Hybrids+for+Cancer+Tri-Therapy:+Interplay+of+Photothermal+Therapy,+Magnetic+Hyperthermia+and+Photodynamic+Therapy.">Iron Oxide Nanoflowers CuS Hybrids for Cancer Tri-Therapy: Interplay of Photothermal Therapy, Magnetic Hyperthermia and Photodynamic Therapy.</a> Theranostics. 9 (5), 1288-1302 (2019).</li><li>Espinosa, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Hyper)Thermia+or+Photothermia?+Progressive+Comparison+of+Iron+Oxide+and+Gold+Nanoparticles+Heating+in+Water,+in+Cells,+and+In+Vivo.">Hyper)Thermia or Photothermia? Progressive Comparison of Iron Oxide and Gold Nanoparticles Heating in Water, in Cells, and In Vivo.</a> Advanced Functional Materials. 28 (37), 1803660 (2018).</li><li>Xu, C., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Magnetic+Hyperthermia+Ablation+of+Tumors+Using+Injectable+Fe(3)O(4)/Calcium+Phosphate+Cement.">Magnetic Hyperthermia Ablation of Tumors Using Injectable Fe(3)O(4)/Calcium Phosphate Cement.</a> ACS Applied Materials &amp; Interfaces. 7 (3), 13866-13875 (2015).</li><li>Wilhelm, S., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Analysis+of+nanoparticle+delivery+to+tumours.">Analysis of nanoparticle delivery to tumours.</a> Nature Reviews Materials. 1, 16014 (2016).</li><li>Chen, H., Zhang, W., Zhu, G., Xie, J., Chen, X. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Rethinking+cancer+nanotheranostics.">Rethinking cancer nanotheranostics.</a> Nature Reviews Materials. 2, (2017).</li><li>Rapoport, N. Y., Kennedy, A. M., Shea, J. E., Scaife, C. L., Nam, K. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Controlled+and+targeted+tumor+chemotherapy+by+ultrasound-activated+nanoemulsions/microbubbles.">Controlled and targeted tumor chemotherapy by ultrasound-activated nanoemulsions/microbubbles.</a> Journal of Controlled Release : The Official Journal of the Controlled Release Society. 138 (3), 268-276 (2009).</li><li>Gao, Y., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Controlled+nanoparticle+release+from+stable+magnetic+microbubble+oscillations.">Controlled nanoparticle release from stable magnetic microbubble oscillations.</a> NPG Asia Materials. 8 (4), 260 (2016).</li><li>Bao, B., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Mussel-inspired+functionalization+of+semiconducting+polymer+nanoparticles+for+amplified+photoacoustic+imaging+and+photothermal+therapy.">Mussel-inspired functionalization of semiconducting polymer nanoparticles for amplified photoacoustic imaging and photothermal therapy.</a> Nanoscale. 11 (31), 14727-14733 (2019).</li><li>Wu, H., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Enhanced+Tumor+Synergistic+Therapy+by+Injectable+Magnetic+Hydrogel+Mediated+Generation+of+Hyperthermia+and+Highly+Toxic+Reactive+Oxygen+Species.">Enhanced Tumor Synergistic Therapy by Injectable Magnetic Hydrogel Mediated Generation of Hyperthermia and Highly Toxic Reactive Oxygen Species.</a> ACS Nano. 13 (12), 14013-14023 (2019).</li><li>Alzaraa, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Targeted+microbubbles+in+the+experimental+and+clinical+setting.">Targeted microbubbles in the experimental and clinical setting.</a> American Journal of Surgery. 204 (3), 355-366 (2012).</li></ol>

著者らは開示するものは何もない。

ここでは、自己集合による酸化鉄ナノ粒子殻付きマイクロバブル(NSM)を、1つのナノ治療プラットフォームで相乗的な磁気、音響、および光学応答性を持つプロトコルを発表した。IONPは空気コアの周りに密に詰め込んで磁気シェルを形成し、ターゲティングのための外部磁場によって制御することができます。一度配信されると、IONPのリリースは、超音波トリガーによって達成することがで?...

がんは最も致命的な病気の1つであり、世界中で毎年何百万人もの死者を出し、経済的損失が大きい1.診療所では、外科的切除、放射線療法、および化学療法などの従来の抗癌療法は、依然として満足のいく治療効果2を提供できない。これらの療法の制限は、高毒性の副作用、高い再発率および高転移率3である。例えば、化学療法は、腫瘍部位4に正確に化学療法の低い送達効率に苦しんでいる。細胞外マトリックスや高腫瘍間質液圧を含む生物学的障壁を越えて腫瘍組織に深く浸透する薬物の不全は、治療効果の低さ5にも関与する。また、腫瘍抵抗は通常、単一の化学療法6によって治療を受けた患者で起こる。そこで、光熱療法(PTT)や磁気高熱療法(MHT)などの腫瘍の熱アブレーションが起こる技術は、腫瘍抵抗性を低減する有望な結果を示しており、臨床試験7、8、9で出現している。
PTTは、レーザーエネルギーの照射下での光熱変換剤の作用により、癌細胞の熱アブレーションを引き起こす。生成された高温(50°C以上)は、完全な細胞壊死を誘発する10。ごく最近、鉄酸化物ナノ粒子(IONP)は、近赤外(NIR)光11によって活性化することができる光熱変換剤であることが実証された。 近赤外域におけるモル吸収係数が低いにもかかわらず、IONPは低温(43°C)光熱療法の候補であり、正常組織への熱暴露による損傷を軽減し、腫瘍転移12に対する抗腫瘍免疫を開始する修飾療法である。PTT の制限の 1 つは、レーザーの低い貫通深さです。深い座った腫瘍については、酸化鉄ナノ粒子の交流磁場(AFM)誘導加熱(磁気高熱と呼ばれる)は、PTT13,14の代替療法である。MHTの主な利点は、磁場15の高い浸透です。しかし、IONPの比較的高濃度が必要なのは、その臨床応用にとって大きな欠点である。動物における固形腫瘍へのナノメディシン(またはナノ粒子)の送達効率は、循環、蓄積、および浸透16、17を含む一連の障害のために1〜10%であった。したがって、高い組織浸透を達成する能力を持つ制御され、標的を絞ったIONPsデリバリー戦略は、がん治療に大きな関心を持っています。
超音波媒介ナノ粒子送達は、マイクロバブルキャビテーション18、19と呼ばれる現象のために、腫瘍組織に深部にナノ粒子の浸透を促進する能力を示している。本研究では、自己集合、磁気、音響、光学応答性を1つのナノ治療プラットフォームで相乗的に行い、IONPsシェルマイクロバブル(NSM)を製造する。NSMには、空気コアと酸化鉄ナノ粒子のシェルが含まれ、直径は約5.4μmです。NSMは、腫瘍部位に磁気的に誘導することができる。その後、IONPの放出は、マイクロバブルキャビテーションとマイクロストリーミングを伴う超音波によって引き起こされます。マイクロストリーミングから受けた運動量は、腫瘍組織へのIONPの浸透を促進する。PTTおよびMHTはNIRレーザー照射かAFMの適用によって、または両方の組合せによって達成することができる。

<table border="0" cellpadding="0" cellspacing="0" style="width:1331px;" width="1330">
	<colgroup>
		<col />
		<col />
		<col />
		<col />
	</colgroup>
	<tbody>
		<tr height="40">
			<td height="40" style="height:40px;width:337px;">808 nm laser power</td>
			<td style="width:315px;">Changchun New Industries Optoelectronics Tech</td>
			<td style="width:263px;">MDL-F-808-5W-18017023</td>
			<td style="width:416px;"></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Calcein-AM</td>
			<td>Thermo Fisher SCIENTIFIC</td>
			<td>C3099</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Fetal bovine serum</td>
			<td>Invitrogen</td>
			<td>16000-044</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Fluorescence Microscope</td>
			<td>Olympus</td>
			<td>IX71</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;">Function generator</td>
			<td>Keysight</td>
			<td>33500B series</td>
			<td style="width:416px;">20 MHz, 2 channels with arbitrary waveform generation capability</td>
		</tr>
		<tr height="48">
			<td height="48" style="height:48px;">Gelatin gel</td>
			<td>Sigma</td>
			<td>9000-70-8</td>
			<td style="width:416px;"></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Heating machine</td>
			<td>Shuangping</td>
			<td>SPG-06- II</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Homemade focused transducer</td>
			<td></td>
			<td></td>
			<td>Frequency=855, R-X=36.2W+5.8W, |Z|-&#952;=37W+8&#176;</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Homogenizer</td>
			<td>SCILOGEX</td>
			<td>D-160</td>
			<td>8000-30000 rpm</td>
		</tr>
		<tr height="41">
			<td height="41" style="height:41px;">Hydrophone</td>
			<td>T&#38;C</td>
			<td>NH1000</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">ICR male mice</td>
			<td>OG Pharmaceutical. Co. Ltd</td>
			<td></td>
			<td>8-week-old</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Inductively coupled plasma optical emission spectrometry</td>
			<td>PerkinElmer</td>
			<td></td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Infrared thermal imaging camera.</td>
			<td>FLIR</td>
			<td>E50</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Iron(II,III) oxide</td>
			<td>Alfa Aesar</td>
			<td>1317-61-9</td>
			<td>50-100nm APS Powder</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Laser power meter</td>
			<td colspan="2">Changchun New Industries Optoelectronics Tech</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Oscilloscope</td>
			<td>Keysight</td>
			<td>DSOX3054T</td>
			<td>Bandwidth 500 MHz, Sampling Rate 5 GS/S, 4 channels</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">RF Power Amplifier</td>
			<td>T&#38;C</td>
			<td>AG1020</td>
			<td style="width:416px;">The signal source can also be connected to an external signal source. The gain can be adjusted from 0 to 100%. It has multiple functions such as frequency sweep, pulse, and triangle.</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Roswell Park Memorial Institute-1640</td>
			<td>KeyGEN BioTECH</td>
			<td>KGM31800</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Sodium dodecyl sulfate</td>
			<td>Sigma</td>
			<td>151-21-3</td>
			<td></td>
		</tr>
	</tbody>
</table>

magnetic-, acoustic-, and optical-triple-responsive microbubbles for magnetic hyperthermia and pothotothermal combination cancer therapy

標的と深く浸透した送達を目指す抗がん剤の精密送達と、腫瘍部位での制御放出が課題となっている。ここでは、自己集合、磁気、音響、光学応答性を1つのナノ治療プラットフォームで相乗化することにより、酸化鉄ナノ粒子殻付きマイクロバブル(NSM)を製造します。酸化鉄ナノ粒子は、磁気と光熱の両方の薬剤として機能します。静脈内注射後、NSMは、腫瘍部位に磁気的に誘導することができる。超音波は酸化鉄ナノ粒子の放出を引き起こし、マイクロバブルのキャビテーション効果のためにナノ粒子の深部腫瘍への浸透を促進する。その後、結合癌治療のために腫瘍に対して磁気温熱療法および光熱療法を行うことができるが、腫瘍不均一性による癌耐性の解決策である。このプロトコルでは、構造、化学的、磁気および音響特性を含むNSMの合成および特性評価が行われた。また、熱療法による抗癌効果について、インビトロ細胞培養を用いて検討した。提案された送達戦略と併用療法は、出産と抗癌の両方の有効性を改善するために癌治療において大きな約束を保持する。

本研究で用いた三重応答性ナノ粒子殻状マイクロバブル(NSM)は、界面活性剤とIONPの混合物を攪拌することによって調製された。IONPs(50 nm)は液体および気体の中心のインターフェイスで自己組み立てられ、密に詰まった磁気シェルを形成する。NSMの形態を 図1Aに示します。結果として得られたNSMは球形を示し、平均直径は5.41±1.78 μm(図1B)を示した。結果は、NSMが正常に...

Watch this Scientific Journal Video about Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy at JoVE.com

Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy

ここでは、自己集合体を介した酸化鉄ナノ粒子殻状マイクロバブル(NSM)の製造プロトコルであり、磁気高熱および光熱併用がん治療のための1つのナノ治療プラットフォームにおける磁気、音響、および光応答性を相乗化する。

磁気温熱療法とポト温熱併用がん治療のための磁気、音響、光三重応答性マイクロバブル

The precision delivery of anti-cancer agents which aim for targeted and deep-penetrated delivery as well as a controlled release at the tumor site has ...

magnetic-acoustic-optical-triple-responsive-microbubbles-for-magnetic

Research

JoVE Journal

Bioengineering

3.0K ビュー.  Nanjing University of Posts & Telecommunications. ここでは、自己集合体を介した酸化鉄ナノ粒子殻状マイクロバブル(NSM)の製造プロトコルであり、磁気高熱および光熱併用がん治療のための1つのナノ治療プラットフォームにおける磁気、音響、および光応答性を相乗化する。

ビデオ: Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy

Magnetic Tweezers for the Measurement of Twist and Torque

Single-molecule techniques make it possible to investigate the behavior of individual biological molecules in solution in real time. These techniques include so-called force spectroscopy approaches such as atomic force microscopy, optical tweezers, flow stretching, and magnetic tweezers. Amongst these approaches, magnetic tweezers have distinguished themselves by their ability to apply torque while maintaining a constant stretching force. Here, it is illustrated how such a &#8220;conventional&#8221; magnetic tweezers experimental configuration can, through a straightforward modification of its field configuration to minimize the magnitude of the transverse field, be adapted to measure the degree of twist in a biological molecule. The resulting configuration is termed the freely-orbiting magnetic tweezers. Additionally, it is shown how further modification of the field configuration can yield a transverse field with a magnitude intermediate between that of the &#8220;conventional&#8221; magnetic tweezers and the freely-orbiting magnetic tweezers, which makes it possible to directly measure the torque stored in a biological molecule. This configuration is termed the magnetic torque tweezers. The accompanying video explains in detail how the conversion of conventional magnetic tweezers into freely-orbiting magnetic tweezers and magnetic torque tweezers can be accomplished, and demonstrates the use of these techniques. These adaptations maintain all the strengths of conventional magnetic tweezers while greatly expanding the versatility of this powerful instrument.

Magnetic tweezers, a powerful single-molecule manipulation technique, can be adapted for the direct measurements of the twist (using a configuration called freely-orbiting magnetic tweezers) and torque (using a configuration termed magnetic torque tweezers) in biological macromolecules. Guidelines for performing such measurements are given, including applications to the study of DNA and associated nucleo-protein filaments.

ツイストとトルクの計測のための磁気ピンセット

Single-molecule techniques make it possible to investigate the behavior of individual biological molecules in solution in real time. These techniques ...

生物工学

Fabrication of a Functionalized Magnetic Bacterial Nanocellulose with Iron Oxide Nanoparticles

In this study, bacterial nanocellulose (BNC) produced by the bacteria Gluconacetobacter xylinus is synthesized and impregnated in situ with iron oxide nanoparticles (IONP) (Fe3O4) to yield a magnetic bacterial nanocellulose (MBNC). The synthesis of MBNC is a precise and specifically designed multi-step process. Briefly, bacterial nanocellulose (BNC) pellicles are formed from preserved G. xylinus strain according to our experimental requirements of size and morphology. A solution of iron(III) chloride hexahydrate (FeCl3&#183;6H2O) and iron(II) chloride tetrahydrate (FeCl2&#183;4H2O) with a 2:1 molar ratio is prepared and diluted in deoxygenated high purity water. A BNC pellicle is then introduced in the vessel with the reactants. This mixture is stirred and heated at 80 &#176;C in a silicon oil bath and ammonium hydroxide (14%) is then added by dropping to precipitate the ferrous ions into the BNC mesh. This last step allows forming in situ magnetite nanoparticles (Fe3O4) inside the bacterial nanocellulose mesh to confer magnetic properties to BNC pellicle. A toxicological assay was used to evaluate the biocompatibility of the BNC-IONP pellicle. Polyethylene glycol (PEG) was used to cover the IONPs in order to improve their biocompatibility. Scanning electron microscopy (SEM) images showed that the IONP were located preferentially in the fibril interlacing spaces of the BNC matrix, but some of them were also found along the BNC ribbons. Magnetic force microscope measurements performed on the MBNC detected the presence magnetic domains with high and weak intensity magnetic field, confirming the magnetic nature of the MBNC pellicle. Young&#39;s modulus values obtained in this work are also in a reasonable agreement with those reported for several blood vessels in previous studies.

Here, we present a protocol to make a bacterial nanocellulose (BNC) magnetic for applications in damaged blood vessel reconstruction. The BNC was synthesized by G. xylinus strain. On the other hand, magnetization of the BNC was realized through in situ precipitation of Fe2+ and Fe3+ ferrous ions inside the BNC mesh.

酸化鉄ナノ粒子との機能を有する磁性細菌Nanocelluloseの作製

In this study, bacterial nanocellulose (BNC) produced by the bacteria Gluconacetobacter xylinus is synthesized and impregnated in situ with iron oxide ...

Custom-designed Laser-based Heating Apparatus for Triggered Release of Cisplatin from Thermosensitive Liposomes with Magnetic Resonance Image Guidance

Liposomes have been employed as drug delivery systems to target solid tumors through exploitation of the enhanced permeability and retention (EPR) effect resulting in significant reductions in systemic toxicity. Nonetheless, insufficient release of encapsulated drug from liposomes has limited their clinical efficacy. Temperature-sensitive liposomes have been engineered to provide site-specific release of drug in order to overcome the problem of limited tumor drug bioavailability. Our lab has designed and developed a heat-activated thermosensitive liposome formulation of cisplatin (CDDP), known as HTLC, to provide triggered release of CDDP at solid tumors. Heat-activated delivery in vivo was achieved in murine models using a custom-built laser-based heating apparatus that provides a conformal heating pattern at the tumor site as confirmed by MR thermometry (MRT). A fiber optic temperature monitoring device was used to measure the temperature in real-time during the entire heating period with online adjustment of heat delivery by alternating the laser power. Drug delivery was optimized under magnetic resonance (MR) image guidance by co-encapsulation of an MR contrast agent (i.e.,&#160;gadoteridol) along with CDDP into the thermosensitive liposomes as a means to validate the heating protocol and to assess tumor accumulation. The heating protocol consisted of a preheating period of 5 min prior to administration of HTLC and 20 min heating post-injection. This heating protocol resulted in effective release of the encapsulated agents with the highest MR signal change observed in the heated tumor in comparison to the unheated tumor and muscle. This study demonstrated the successful application of the laser-based heating apparatus for preclinical thermosensitive liposome development and the importance of MR-guided validation of the heating protocol for optimization of drug delivery.

AN MRI-compatible&#160;custom-designed laser-based heating apparatus has been developed to provide local heating of subcutaneous tumors in order to activate release of agents from thermosensitive liposomes specifically at the tumor region.

磁気共鳴画像誘導による感熱リポソームからのシスプラチンのトリガリリースのためのカスタム設計されたレーザーベースの加熱装置

Liposomes have been employed as drug delivery systems to target solid tumors through exploitation of the enhanced permeability and retention (EPR) effect ...

Rapid Scan Electron Paramagnetic Resonance Opens New Avenues for Imaging Physiologically Important Parameters In Vivo

We demonstrate a superior method of 2D spectral-spatial imaging of stable radical reporter molecules at 250 MHz using rapid-scan electron-paramagnetic-resonance (RS-EPR), which can provide quantitative information under in vivo conditions on oxygen concentration, pH, redox status and concentration of signaling molecules (i.e., OH&#8226;, NO&#8226;). The RS-EPR technique has a higher sensitivity, improved spatial resolution (1 mm), and shorter acquisition time in comparison to the standard continuous wave (CW) technique. A variety of phantom configurations have been tested, with spatial resolution varying from 1 to 6 mm, and spectral width of the reporter molecules ranging from 16 &#181;T (160 mG) to 5 mT (50 G). A cross-loop bimodal resonator decouples excitation and detection, reducing the noise, while the rapid scan effect allows more power to be input to the spin system before saturation, increasing the EPR signal. This leads to a substantially higher signal-to-noise ratio than in conventional CW EPR experiments.

Rapid Scan Electron Paramagnetic Resonance Opens New Avenues for Imaging Physiologically Important Parameters In Vivo

A new electron paramagnetic resonance (EPR) method, rapid scan EPR (RS-EPR), is demonstrated for 2D spectral spatial imaging which is superior to the traditional continuous wave (CW) technique and opens new venues for in vivo imaging. Results are demonstrated at 250 MHz, but the technique is applicable at any frequency.

高速走査電子常磁性共鳴イメージング生理学的に重要なパラメータのための新しい道を開きます。<em&gt;インビボ</em

We demonstrate a superior method of 2D spectral-spatial imaging of stable radical reporter molecules at 250 MHz using rapid-scan ...

Magnetic Levitation Coupled with Portable Imaging and Analysis for Disease Diagnostics

Currently, many clinical diagnostic procedures are complex, costly, inefficient, and inaccessible to a large population in the world. The requirements for specialized equipment and trained personnel require that many diagnostic tests be performed at remote, centralized clinical laboratories. Magnetic levitation is a simple yet powerful technique and can be applied to levitate cells, which are suspended in a paramagnetic solution and placed in a magnetic field, at a position determined by equilibrium between a magnetic force and a buoyancy force. Here, we present a versatile platform technology designed for point-of-care diagnostics which uses magnetic levitation coupled to microscopic imaging and automated analysis to determine the density distribution of a patient's cells as a useful diagnostic indicator. We present two platforms operating on this principle: (i) a smartphone-compatible version of the technology, where the built-in smartphone camera is used to image cells in the magnetic field and a smartphone application processes the images and to measures the density distribution of the cells and (ii) a self-contained version where a camera board is used to capture images and an embedded processing unit with attached thin-film-transistor (TFT) screen measures and displays the results. Demonstrated applications include: (i) measuring the altered distribution of a cell population with a disease phenotype compared to a healthy phenotype, which is applied to sickle cell disease diagnosis, and (ii) separation of different cell types based on their characteristic densities, which is applied to separate white blood cells from red blood cells for white blood cell cytometry. These applications, as well as future extensions of the essential density-based measurements enabled by this portable, user-friendly platform technology, will significantly enhance disease diagnostic capabilities at the point of care.

We present a magnetic levitation technique coupled with automated imaging and analysis in both a smartphone-compatible device and a device with embedded imaging and processing. This is applied to measure the density distribution of cells with two demonstrated biomedical applications: sickle cell disease diagnosis and separating white and red blood cells.

病の診断のためのポータブルイメージングおよび分析と相まって磁気浮上

Currently, many clinical diagnostic procedures are complex, costly, inefficient, and inaccessible to a large population in the world. The requirements for ...

3D Magnetic Stem Cell Aggregation and Bioreactor Maturation for Cartilage Regeneration

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach recently explored for the development of autologous replacements involves the differentiation of stem cells into chondrocytes. To initiate this chondrogenesis, a degree of compaction of the stem cells is required; hence, we demonstrated the feasibility of magnetically condensing cells, both within thick scaffolds and scaffold-free, using miniaturized magnetic field sources as cell attractors. This magnetic approach was also used to guide aggregate fusion and to build scaffold-free, organized, three-dimensional (3D) tissues several millimeters in size. In addition to having an enhanced size, the tissue formed by magnetic-driven fusion presented a significant increase in the expression of collagen II, and a similar trend was observed for aggrecan expression. As the native cartilage was subjected to forces that influenced its 3D structure, dynamic maturation was also performed. A bioreactor that provides mechanical stimuli was used to culture the magnetically seeded scaffolds over a 21-day period. Bioreactor maturation largely improved chondrogenesis into the cellularized scaffolds; the extracellular matrix obtained under these conditions was rich in collagen II and aggrecan. This work outlines the innovative potential of magnetic condensation of labeled stem cells and dynamic maturation in a bioreactor for improved chondrogenic differentiation, both scaffold-free and within polysaccharide scaffolds.

Chondrogenesis from stem cells requires fine tuning the culture conditions. Here, we present a magnetic approach for condensing cells, an essential step to initiate chondrogenesis. In addition, we show that dynamic maturation in a bioreactor applies mechanical stimulation to the cellular constructs and enhances cartilaginous extracellular matrix production.

軟骨再生のための3次元磁気幹細胞凝集およびバイオリアクター成熟

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach ...

Magnetic and Thermal-sensitive Poly(N-isopropylacrylamide)-based Microgels for Magnetically Triggered Controlled Release

Magnetically and thermally sensitive poly(N-isopropylacrylamide) (PNIPAAm)/Fe3O4-NH2 microgels with the encapsulated anti-cancer drug curcumin (Cur) were designed and fabricated for magnetically triggered release. PNIPAAm-based magnetic microgels with a spherical structure were produced via a temperature-induced emulsion followed with physical-crosslinking by mixing PNIPAAm, polyethylenimine (PEI), and Fe3O4-NH2 magnetic nanoparticles. Because of their dispersity, the Fe3O4-NH2 nanoparticles were embedded inside the polymer matrix. The amine groups exposed on the Fe3O4-NH2 and PEI surface supported the spherical structure by physically crosslinking with the amide groups of the PNIPAAm. The hydrophobic anti-cancer drug curcumin can be dispersed in water after encapsulation into the microgels. The microgels were characterized by transmission electron microscopy (TEM), Fourier transform infrared spectroscopy (FT-IR), and UV-Vis spectral analysis. Furthermore, magnetically triggered release was studied under an external high frequency magnetic field (HFMF). A significant &#34;burst release&#34; of curcumin was observed after applying the HFMF to the microgels due to the magnetic inductive heating (hyperthermia) effect. This manuscript describes the magnetically triggered controlled release of Cur-PNIPAAm/Fe3O4-NH2 encapsulated curcumin, which can be potentially applied for tumor therapy.

Magnetic and Thermal-sensitive PolyN-isopropylacrylamide-based Microgels for Magnetically Triggered Controlled Release

This manuscript describes the preparation of magnetic and thermal-sensitive microgels via a temperature-induced emulsion without chemical reaction. These sensitive microgels were synthesized by mixing poly(N-isopropylacrylamide) (PNIPAAm), polyethylenimine (PEI) and Fe3O4-NH2 nanoparticles for the potential use in magnetically and thermally triggered drug-release.

磁気および感熱性ポリ（<em&gt; N</em&gt; - イソプロピルアクリルアミド）ベースのミクロゲル

Magnetically and thermally sensitive poly(N-isopropylacrylamide) (PNIPAAm)/Fe3O4-NH2 microgels with the encapsulated anti-cancer drug curcumin (Cur) were ...

Metabolic Support of Excised, Living Brain Tissues During Magnetic Resonance Microscopy Acquisition

This protocol describes the procedures necessary to support normal metabolic functions of acute brain slice preparations during the collection of magnetic resonance (MR) microscopy data. While it is possible to perform MR collections on living, excised mammalian tissue, such experiments have traditionally been constrained by resolution limits and are thus incapable of visualizing tissue microstructure. Conversely, MR protocols that did achieve microscopic image resolution required the use of fixed samples to accommodate the need for static, unchanging conditions over lengthy scan times. The current protocol describes the first available MR technique that enables imaging of living, mammalian tissue samples at microscopic resolutions. Such data is of great importance to the understanding of how pathology-based contrast changes occurring at the microscopic level influence the content of macroscopic MR scans such as those used in the clinic. Once such an understanding is realized, diagnostic methods with greater sensitivity and accuracy can be developed, which will translate directly to earlier disease treatment, more accurate therapy monitoring and improved patient outcomes.
While the described methodology focuses on brain slice preparations, the protocol is adaptable to any excised tissue slice given that changes are made to the gas and perfusate preparations to accommodate the tissue&#39;s specific metabolic needs. Successful execution of the protocol should result in living, acute slice preparations that exhibit MR diffusion signal stability for periods up to 15.5 h. The primary advantages of the current system over other MR compatible perfusion apparatuses are its compatibility with the MR microscopy hardware required to attain higher resolution images and ability to provide constant, uninterrupted flow with carefully regulated perfusate conditions. Reduced sample throughput is a consideration with this design as only one tissue slice may be imaged at a time.

The current protocol describes a method by which users can maintain viability of acute hippocampal and cortical slice preparations during the collection of magnetic resonance microscopy data.

代謝サポートの切除、生体脳磁気共鳴顕微鏡集録時に

This protocol describes the procedures necessary to support normal metabolic functions of acute brain slice preparations during the collection of magnetic ...

Optimized Setup and Protocol for Magnetic Domain Imaging with In Situ Hysteresis Measurement

This paper elaborates the sample preparation protocols required to obtain optimal domain patterns using the Bitter method, focusing on the extra steps compared to standard metallographic sample preparation procedures. The paper proposes a novel bespoke rig for dynamic domain imaging with in situ BH (magnetic hysteresis) measurements and elaborates the protocols for the sensor preparation and the use of the rig to ensure accurate BH measurement. The protocols for static and ordinary dynamic domain imaging (without in situ BH measurements) are also presented. The reported method takes advantage of the convenience and high sensitivity of the traditional Bitter method and enables in situ BH measurement without interrupting or interfering with the domain wall movement processes. This facilitates establishing a direct and quantitative link between the domain wall movement processes&#8211;microstructural feature interactions in ferritic steels with their BH loops. This method is anticipated to become a useful tool for the fundamental study of microstructure&#8211;magnetic property relationships in steels and to help interpret the electromagnetic sensor signals for non-destructive evaluation of steel microstructures.

Optimized Setup and Protocol for Magnetic Domain Imaging with In Situ Hysteresis Measurement

This paper elaborates the sample and sensor preparation procedures and the protocols for using the test rig particularly for dynamic domain imaging with in situ BH measurements in order to achieve optimal domain pattern quality and accurate BH measurements.

最適化されたセットアップおよびヒステリシス測定場の磁区イメージングのためのプロトコル

This paper elaborates the sample preparation protocols required to obtain optimal domain patterns using the Bitter method, focusing on the extra steps ...

Protocol for MicroRNA Transfer into Adult Bone Marrow-derived Hematopoietic Stem Cells to Enable Cell Engineering Combined with Magnetic Targeting

While CD133+ hematopoietic stem cells (SCs) have been proven to provide high potential in the field of regenerative medicine, their low retention rates after injection into injured tissues as well as the observed massive cell death rates lead to very restricted therapeutic effects. To overcome these limitations, we sought to establish a non-viral based protocol for suitable cell engineering prior to their administration. The modification of human CD133+ expressing SCs using microRNA (miR) loaded magnetic polyplexes was addressed with respect to uptake efficiency and safety as well as the targeting potential of the cells. Relying on our protocol, we can achieve high miR uptake rates of 80&#8211;90% while the CD133+ stem cell properties remain unaffected. Moreover, these modified cells offer the option of magnetic targeting. We describe here a safe and highly efficient procedure for the modification of CD133+ SCs. We expect this approach to provide a standard technology for optimization of therapeutic stem cell effects and for monitoring of the administered cell product via magnetic resonance imaging (MRI).

This protocol illustrates a safe and efficient procedure to modify CD133+ hematopoietic stem cells. The presented non-viral, magnetic polyplex-based approach may provide a basis for the optimization of therapeutic stem cell effects as well as for monitoring the administered cell product via magnetic resonance imaging.

成人骨髄由来造血幹細胞が細胞工学磁気ターゲッティングと結合を有効にするにマイクロ Rna の転送のためのプロトコル

While CD133+ hematopoietic stem cells (SCs) have been proven to provide high potential in the field of regenerative medicine, their low retention rates ...