وأيد هذا العمل من قبل مؤسسة البحوث الوطنية في سنغافورة من قبل أحد مراكز البحوث في التميز، ومعهد Mechanobiology، سنغافورة يديرها. ويدعم MFAC وكالة للعلوم والتكنولوجيا والبحوث (سنغافورة) والوكالة الوطنية للبحوث (فرنسا) برنامج مشترك تحت رقم المشروع ويدعم 1122703037. BKKT من قبل معهد Mechanobiology. نشكر السيد دانيال HC ونغ لالمخطوط والسيدة الفجر JH الجدد للمساعدة في إنتاج الفيديو القراءة دليل على ذلك.

1. إعداد حلول متضاعف الكتروليتي <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> تنقية الشيتوزان، كما هو مفصل في لياو وآخرون لفترة وجيزة، وخلق 1٪ (ث / ت) حل الشيتوزان في 2٪ (ت / ت) وحامض الخليك وفراغ مرشح يستخدم الصف 93 ورقة الترشيح. تحييد الترشيح باستخدام 5M هيدروكسيد الصوديوم حتى استقرت درجة الحموضة إلى 7. الطرد المركزي الشيتوزان عجلت في 1200 x ج لمدة 10 دقيقة. صب طاف وإضافة الماء منزوع الأيونات لغسل الشيتوزان. كرر الخطوة الطرد المركزي وغسل مرتين أخريين. تجميد الشيتوزان عجلت في -80 ° C ويجفد O / N للحصول على شكل منقى. تخزين الشيتوزان النقي في خزانة جفف. </li><li style=";text-align:right;direction:rtl"> تزن من 1 غرام من الشيتوزان تنقيته في طبق نسيج الثقافة العقيمة. وضع الشيتوزان في صحن زراعة الأنسجة في أقرب وقت ممكن إلى مصباح الأشعة فوق البنفسجية في مجلس الوزراء السلامة البيولوجية وفضح لضوء الأشعة فوق البنفسجية لمدة 15 دقيقة. باستخدام ملقط معقم، ضع الشيتوزان تعقيمها في وعاء زجاجي. حل الشيتوزان باستخدام تصفية 0.15M حامض الخليك إلى التركيز النهائي بين 0.5٪ و 1٪ (ث / ت). </li><li style=";text-align:right;direction:rtl"> تزن من 0،1 غرام من ملح الصوديوم حمض الألجنيك وتذوب في 10 مل المقطر منزوع الأيونات (DDI) الماء للحصول على 1٪ (ث / ت) حل. خلط الألجنيك ملح الصوديوم حمض لا يقل عن 2 ساعة على خلاط دوامة لضمان حل كامل. تصفية الحل الجينات من خلال 0.2 ميكرون فلتر حقنة. تخزين حل الجينات في 4 ° C. </li><li style=";text-align:right;direction:rtl"> إعادة تشكيل عوامل النمو المؤتلف الإنسان مثل الأوعية الدموية (عامل نمو بطانة VEGF) أو بيتا - عامل نمو الأعصاب (NGF)، على النحو الموصى به من قبل الشركة المصنعة. </li></ol> 2. رسم من ألياف IPC <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> مزيج البروتينات وعوامل النمو أو الجزيئات الحيوية الأخرى في 10-20 ميكرولتر قسامة من الحل متضاعف الكتروليتي له تهمة صافي مماثل. الجزيئات البيولوجية مع صافي شحنة سالبة (مثل الأبقار مصل الزلال [BSA]) ينبغي أن تكون مختلطة مع حل الجينات. الجزيئات البيولوجية مع صافي شحنة موجبة (مثل VEGF) ينبغي أن تكون مختلطة معحل الشيتوزان. </li><li style=";text-align:right;direction:rtl"> وضع قسامات صغيرة (10-20 ميكرولتر) من الشيتوزان والجينات على سطح مستو مستقر التي يتم تغطيتها مع parafilm. يجب وضع قطرات من الشيتوزان والجينات على مقربة ولكن ليس على اتصال مع بعضها البعض. </li><li style=";text-align:right;direction:rtl"> بخفة تراجع كل طرف على زوج من الملقط في الشيتوزان والجينات قطرات. جعل قطرات من polyelectrolytes معا عن طريق معسر ملقط. عندما تأتي قطرات في اتصال مع بعضها البعض، وسحب ببطء ملقط عموديا إلى أعلى لرسم الألياف IPC من واجهة من قطرات اثنين (الشكل 1A). </li><li style=";text-align:right;direction:rtl"> وضع بعناية نهاية الألياف IPC المرسومة على ملقط على الجمع، مثل سقالة البوليمرية مسطحة الملصقة على مغزل الدورية (انظر القسم 3 و 4). تدوير مغزل بسرعة ثابتة من 10 ملم / ثانية للسماح بتشكيل موحدة وbeadless الألياف IPC. زيادة سرعة رسم الألياف IPC سيشكل الخرز، والتي سوف تتسبب في إطلاق موجة من إدراجهاالكيمياء الحيوية وسابق لأوانه إنهاء الألياف. 10 </li><li style=";text-align:right;direction:rtl"> لتحديد كفاءة التأسيس، وجمع كل السوائل المتبقية تركت على parafilm عن طريق تمييع مع 500 ميكرولتر من 1X الفوسفات مخزنة المالحة (PBS). قياس البروتين أو نمو المحتوى عامل في بقايا من خلال فحص BCA (لBSA)، ELISA (لVEGF وNGF) أو فحص المناسب للكشف عن جزيء حيوي يدمج. </li></ol> 3. تصنيع المركب هيدروجيل سقالة من Pullulan-ديكستران (PD) السكاريد وألياف IPC <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> افتعال إطار pullulan الأضاحي لIPC جمع الألياف <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> تزن من السكاريد pullulan وتخلط مع منزوع الأيونات المقطر (DDI) الماء لخلق 20٪ (وزن / حجم) محلول مائي. مزيج الحل pullulan O / N لضمان التجانس. </li><li style=";text-align:right;direction:rtl"> يلقي 15 غرام من حل pullulan إلى 10 سم زراعة الأنسجة قطر البوليسترين (برنامج التعاون الفني) الطبق. تجفيف حل pullulan O / N عند 37 درجة مئوية. قطع الأفلام pullulan إلى 7مم × 7 ملم إطارات مربع. </li></ol></li><li style=";text-align:right;direction:rtl"> إعداد الحل السكاريد-pullulan ديكستران <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> إنشاء 30٪ (ث / ت) حل من السكريات pullulan وديكستران (3: 1 نسبة) في المياه DDI. مزيج O / N لضمان تجانس الحل السكاريد. إضافة ببطء في بيكربونات الصوديوم إلى حل السكاريد لتحقيق تركيز النهائي من 20٪ (ث / ت). مزيج O / N لضمان تجانس الحل. تخزين حل السكاريد في 4 ° C. </li></ol></li><li style=";text-align:right;direction:rtl"> جمع الألياف IPC في إطار pullulan <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> يضعوا إطار pullulan الأضاحي (القسم 3.1) باستخدام مشبك التمساح. عصا مقطع التمساح والإطار pullulan في نهاية مغزل الدورية باستخدام الشريط المغلفة بلاستيكية لاصقة. تدوير مغزل مع الإطار اضافته بسرعة ثابتة من 10 ملم / ثانية. يمكن اضافته إطار pullulan على مغزل الدورية في التوجهات المطلوبة. </li></ol></li><li style=";text-align:right;direction:rtl"> رسم الألياف IPC باستخدام زوج من ملقط (القسم 1) واتاكح نهاية استخلاصها من الألياف IPC على الإطار pullulan الدورية. رسم الألياف IPC بسرعة ثابتة. عند الوصول إلى نهاية طرفية من الألياف IPC، تجفيف بناء O الألياف على الإطار / N في RT. </li><li style=";text-align:right;direction:rtl"> دمج الألياف IPC إلى PD هيدروجيل سقالة </li><li style=";text-align:right;direction:rtl"> لتشعبي كل غرام من حل pullulan ديكستران، إضافة 100 ميكرولتر من 11٪ (ث / ت) الصوديوم trimetaphosphate محلول مائي وهيدروكسيد الصوديوم 100 ميكرولتر 10M 7 مزيج الحل في 60 دورة في الدقيقة باستخدام stirplate عن 1-2 دقائق. بعد إضافة trimetaphosphate الصوديوم وهيدروكسيد الصوديوم، فإن الحل السكاريد تشعبي على الفور تقريبا. من أجل حل السكاريد لزج على بناء الألياف على الإطار إلى تضمين بالكامل الألياف IPC. احتضان الألياف pullulan-ديكستران-IPC مجتمعة (PD-IPC) عند 60 درجة مئوية لمدة 30 دقيقة لتشكيل السقالات مركب crosslinked كيميائيا (الشكل 1B). </li><li style=";text-align:right;direction:rtl"> تنبيه: تنفيذ الخطوة 3.3.2 في غطاء الدخان واستخدام متساو واقية السليمpment باسم حمض الخليك هو تآكل وقابل للاشتعال. </li><li style=";text-align:right;direction:rtl"> للحث على تشكيل مسام في سقالة PD-IPC، غمر سقالة كاملة في 20٪ (ث / ت) وحامض الخليك لمدة 20 دقيقة. </li><li style=";text-align:right;direction:rtl"> إزالة الكواشف غير المتفاعل عن طريق الغسيل-PD IPC السقالات في برنامج تلفزيوني 1X لمدة 5 دقائق في حين تهتز في 100 دورة في الدقيقة. كرر هذه الخطوة 2 مرات. </li><li style=";text-align:right;direction:rtl"> إزالة PBS الزائدة وتجميد فورا السقالات-PD IPC في -80 درجة CO / N. يجفد السقالات لا يقل عن 24 ساعة قبل الاستخدام في أي إصدار أو النشاط الحيوي المقايسات التي تسيطر عليها. </li></ol> 4. تصنيع المركب سقالة من PCL وألياف IPC تنبيه: ثنائي كلورو ميثان هو مادة خطرة. استخدام غطاء الدخان ومعدات الوقاية الشخصية عند التعامل مع ثنائي كلورو ميثان. <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> خلق البكر ونمط PDMS ركائز <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> إنشاء polydimethylsiloxane البكر (PDMS) الركيزة المرنة باستخدام قطعة من برامج التعاون الفني من البعد المطلوب باستخدام عملية الطباعة الحجرية الناعمة. إنشاء pattePDMS rned ركائز باستخدام أساليب الطباعة الحجرية الناعمة القياسية على بولي (ميتاكريليت الميثيل) قوالب مع التضاريس المطلوب. 12 </li></ol></li><li style=";text-align:right;direction:rtl"> افتعال الأضاحي إطار PCL لIPC جمع الألياف <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> تزن خارج PCL وتذوب في ثنائي كلورو ميثان لخلق 0.9٪ (ث / ت) حل. لكل 1 سم 2 مساحة الركيزة PDMS، إسقاط 500 ميكرولتر من 0.9٪ محلول PCL. السماح لجميع من المذيب ثنائي كلورو ميثان لتتبخر تماما في غطاء الدخان. تكرار عملية صب 0.9٪ PCL لرشاقته الفيلم للسمك المطلوب. إزالة الفيلم PCL المجففة من الركيزة PDMS. خلق ثقب في الإطار PCL باستخدام الناخس مناسبة الحجم. 2 </li></ol></li><li style=";text-align:right;direction:rtl"> جمع الألياف IPC على الإطار PCL <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> يضعوا إطار PCL الأضاحي مع فتحة (من 4.2.1) على مقطع التمساح. عصا مقطع التمساح على مغزل الدورية باستخدام الشريط المغلفة بلاستيكية لاصقة. نعلق نهاية استخلاصها من الألياف IPC على فرام PCLه قبل بدء الدوران بسرعة ثابتة من 10MM / ثانية (القسم 2). بعد نهاية الألياف IPC الرسم، تجفيف الألياف على الإطار بناء O / N عند 4 درجات مئوية. </li></ol></li><li style=";text-align:right;direction:rtl"> دمج الألياف على الإطار بناء إلى الركيزة PCL منقوشة <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> إسقاط 500 ميكرولتر من 0.9٪ محلول PCL على الركيزة PDMS لإنشاء قاعدة البكر PCL أو منقوشة، كما هو مطلوب. يلقي طبقات متعددة من 0.9٪ محلول PCL للحصول على سقالة مع سمك المطلوب. السماح لجميع من المذيب ثنائي كلورو ميثان لتتبخر تماما في غطاء الدخان. </li><li style=";text-align:right;direction:rtl"> وضع بناء الألياف على الإطار (القسم 4.3.1) على رأس القاعدة PCL. إضافة 0.9٪ محلول PCL على الألياف في إطار بناء عدة مرات للحصول على سمك المطلوب وتضمين بالكامل الألياف IPC، افتعال سقالة المركبة PCL-IPC (الشكل 1C). </li></ol></li></ol> 5. قياس الإفراج عن العوامل البيولوجية من مركب IPC السقالات <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> وضع مركب PD-IPC أوالسقالات PCL-IPC وقائمة بذاتها الألياف IPC بشكل منفصل في 24 لوحة جيدا. </li><li style=";text-align:right;direction:rtl"> تزج السقالة وقائمة بذاتها الألياف IPC مع 500 ميكرولتر من 1X PBS. احتضان العينات عند 37 ° C. جمع PBS في نقاط زمنية مختلفة (وسائل الإعلام الإفراج) واستبدالها مع 500 ميكرولتر من 1X PBS. </li><li style=";text-align:right;direction:rtl"> قياس كمية البروتين أو عامل النمو في وسائل الإعلام الإفراج باستخدام مقايسة BCA (BSA)، ELISA (VEGF وNGF) أو غيرها من الفحص المناسب لحساب الشخصي الإفراج التراكمي لجزيء حيوي يدمج. </li></ol> 6. البذر من الخلايا على مركب IPC السقالات لاختبار النشاط الحيوي للعوامل البيولوجية المفرج عنهم <ol style=";text-align:right;direction:rtl"><li style=";text-align:right;direction:rtl"> تعقيم PD-IPC أو PCL-IPC السقالات المركبة مجفف بالتجميد باستخدام الأشعة فوق البنفسجية في مجلس الوزراء السلامة البيولوجية لمدة 20 دقيقة على الأقل. </li><li style=";text-align:right;direction:rtl"> استخدام تقنيات زراعة الخلايا القياسية للحصول على تعليق خلية من 2 × 10 5 خلايا في 200 سائط النمو ميكرولتر. البذور تعليق خلية مركزة على السقالات المركبة. بعد عملية الشراءص 20 دقيقة، وأعلى ما يصل حجم من وسائط النمو إلى غمر كامل السقالات. </li><li style=";text-align:right;direction:rtl"> قياس نشاط الخلايا من خلال تقنيات القياسية مثل الامار الأيض الأزرق فحص النشاط، PC12 ثمرة neurite فحص أو المناعي. </li></ol>

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W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Controlled+release+from+fibers+of+polyelectrolyte+complexes.">Controlled release from fibers of polyelectrolyte complexes.</a> J. Control. Release. 104 (2), 347-358 (2005).</li><li>Wan, A. C. A., Liao, I. C., Yim, E. K. F., Leong, K. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Mechanism+of+fiber+formation+by+interfacial+polyelectrolyte+complexation.">Mechanism of fiber formation by interfacial polyelectrolyte complexation.</a> Macromolecules. 37 (18), 7019-7025 (2004).</li><li>Yim, E. K. F., Reano, R., Pang, S., Yee, A., Chen, C., Leong, K. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nanopattern-induced+changes+in+morphology+and+motility+of+smooth+muscle+cells.">Nanopattern-induced changes in morphology and motility of smooth muscle cells.</a> Biomaterials. 26 (26), 5405-5413 (2005).</li><li>Sun, H., Xu, F., Guo, D., Yu, H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Preparation+and+evaluation+of+NGF-microsphere+conduits+for+regeneration+of+defective+nerves.">Preparation and evaluation of NGF-microsphere conduits for regeneration of defective nerves.</a> Neurol. Res. 34 (5), 491-497 (2012).</li><li>Sim&#243;n-Yarza, T., Formiga, F. R., Tamayo, E., Pelacho, B., Prosper, F., Blanco-Prieto, M. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=PEGylated-PLGA+microparticles+containing+VEGF+for+long+term+drug+delivery.">PEGylated-PLGA microparticles containing VEGF for long term drug delivery.</a> Int. J. Pharm. 440 (1), 13-18 (2013).</li><li>Patel, Z. S., Ueda, H., Yamamoto, M., Tabata, Y., Mikos, A. G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=In+vitro+and+in+vivo+release+of+vascular+endothelial+growth+factor+from+gelatin+microparticles+and+biodegradable+composite+scaffolds.">In vitro and in vivo release of vascular endothelial growth factor from gelatin microparticles and biodegradable composite scaffolds.</a> Pharm. Res. 25 (10), 2370-2378 (2008).</li><li>Sun, H., Xu, F., Guo, D., Liu, G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=In+vitro+evaluation+of+the+effects+of+various+additives+and+polymers+on+nerve+growth+factor+microspheres.">In vitro evaluation of the effects of various additives and polymers on nerve growth factor microspheres.</a> Drug Dev. Int. Pharm. 40 (4), 452-457 (2014).</li><li>Lee, P. I. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Kinetics+of+drug+release+from+hydrogel+matrices.">Kinetics of drug release from hydrogel matrices.</a> J. Control. Release. 2, 277-288 (1985).</li><li>Cutiongco, M. F. A., Choo, R. K. T., Shen, N. J. X., Chua, B. M. X., Sju, E., Choo, A. W. L., Le Visage, C., Yim, E. K. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Composite+scaffold+of+poly(vinyl+alcohol)+and+interfacial+polyelectrolyte+complexation+fibers+for+controlled+biomolecule+delivery.">Composite scaffold of poly(vinyl alcohol) and interfacial polyelectrolyte complexation fibers for controlled biomolecule delivery.</a> Front. Bioeng. Biotechnol. 3 (3), 1-12 (2015).</li><li>Yow, S. Z., Lim, T. H., Yim, E. K. F., Lim, C. T., Leong, K. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+3D+Electroactive+Polypyrrole-Collagen+Fibrous+Scaffold+for+Tissue+Engineering.">A 3D Electroactive Polypyrrole-Collagen Fibrous Scaffold for Tissue Engineering.</a> Polymers. 3 (1), 527-544 (2011).</li><li>Leong, M. F., Toh, J. K. 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=Patterned+prevascularised+tissue+constructs+by+assembly+of+polyelectrolyte+hydrogel+fibres.">Patterned prevascularised tissue constructs by assembly of polyelectrolyte hydrogel fibres.</a> Nat. Commun. 4, 2353 (2013).</li><li>Di Benedetto, F., Biasco, A., Pisignano, D., Cingolani, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Patterning+polyacrylamide+hydrogels+by+soft+lithography.">Patterning polyacrylamide hydrogels by soft lithography.</a> Nanotechnology. 16 (5), S165 (2005).</li><li>Revzin, A., Russell, R. J., 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=Fabrication+of+poly(ethylene+glycol)+hydrogel+microstructures+using+photolithography.">Fabrication of poly(ethylene glycol) hydrogel microstructures using photolithography.</a> Langmuir. 17 (18), 5440-5447 (2001).</li><li>Yim, E. K. F., Liao, I. C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Tissue+compatibility+of+interfacial+polyelectrolyte+complexation+fibrous+scaffold:+evaluation+of+blood+compatibility+and+biocompatibility.">Tissue compatibility of interfacial polyelectrolyte complexation fibrous scaffold: evaluation of blood compatibility and biocompatibility.</a> Tissue Eng. Part A. 13 (2), 423-433 (2007).</li><li>Chaouat, M., Le Visage, C., Autissier, A., Chaubet, F., Letourneur, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+evaluation+of+a+small-diameter+polysaccharide-based+arterial+graft+in+rats.">The evaluation of a small-diameter polysaccharide-based arterial graft in rats.</a> Biomaterials. 27, 5546-5553 (2006).</li><li>Eshraghi, S., Das, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Mechanical+and+microstructural+properties+of+polycaprolactone+scaffolds+with+one-dimensional,+two+dimensional,+and+three-dimensional+orthogonally+oriented+porous+architectures+produced+by+selective+laser+sintering.">Mechanical and microstructural properties of polycaprolactone scaffolds with one-dimensional, two dimensional, and three-dimensional orthogonally oriented porous architectures produced by selective laser sintering.</a> Acta Biomater. 6, 2467-2476 (2010).</li></ol>

The authors have nothing to disclose.

تتشكل الألياف IPC بتفاعل اثنين polyelectrolytes اتهم معاكس. عملية تستخدم لاستخراج مجمع من واجهة من polyelectrolytes، وتسهيل عملية التجميع الذاتي لتشكيل الألياف مستقر. آلية تشكيل الألياف IPC يضمن أن أي جزيء حيوي أضاف ضمن يمكن إدراجها في متضاعف الكتروليتي اتهم بالمثل أثناء عملية complexation...

The extracellular matrix has inherent biochemical and biophysical cues that direct cell behaviors. Mimicking this physiological three-dimensional (3D) microenvironment is a widely explored strategy for regenerative medicine and tissue engineering applications. For example, both naturally-derived and synthetic substrates have been modified with topographical cues as a means to mimic the biophysical cellular environment.1 For example, polycaprolactone (PCL) scaffolds can be easily patterned by casting on patterned PDMS substrates.2 However, most synthetic scaffolds inadequately recapitulate the controlled biochemical environment in vivo. Bulk or surface modification of synthetic materials only present biochemical cues for cell attachment but still lack temporal regulation of biochemical delivery.3 Thus, there is a need for optimal scaffolds that can mimic the temporally regulated biochemical delivery system of the extracellular matrix. 
Biochemical delivery systems such as microspheres are plagued by problems of loss of bioactivity and low incorporation efficiency due to the severity and complexity of multi-step synthesis process.4-6 Alternative methods that use a one-step fabrication and incorporation method were proven to have excellent potential to create a favorable biochemical microenvironment without the accompanying inefficiency in incorporation and loss of bioactivity. One viable solution is the use of interfacial polyelectrolyte complexation (IPC) fibers to deliver and protect biological agents. When two oppositely charged polyelectrolyte aqueous solutions are brought together, IPC fibers can be drawn out from the interface. Virtually any type of hydrophlic biomolecule in aqueous solution can be added into either the negatively- or positively-charged polyelectrolyte solution, thus facilitating the incorporation of useful biomolecules into the IPC fiber during the complexation process. Furthermore, this process only requires aqueous and ambient conditions, thereby decreasing the risk of loss of bioactivity. Using this method, active growth factors2,7 even cells8,9 have been successfully delivered. In addition, the simple method of forming IPC fibers allows molding into any shape or orientation. The stability of such fibers has been advantageous in its incorporation into both hydrophobic2 and hydrophilic polymers7 to create composite scaffolds. These composite scaffolds with IPC fibers are beneficial for creating a physiologically relevant biochemical environment while providing physical anchorage for cells. 
In this study, we show a method to incorporate IPC fibers into a hydrophilic and a hydrophobic scaffold with topography for controlled release of active biomolecules. As a proof-of-concept, we incorporate IPC fibers made from chitosan and alginate into the biocompatible, non-immunogenic and non-antigenic pullulan-dextran hydrophilic hydrogel or the biocompatible polycaprolactone hydrophobic scaffold.

<table border="0" cellpadding="0" cellspacing="0">
	<tbody>
		<tr>
			<td>Pullulan&#160;</td>
			<td>Hayashibara Inc Okayama Japan</td>
			<td></td>
			<td>Molecular weight (MW) 200 kDa. This material is pharmaceutical grade pullulan used to make pullulan frames and PD-IPC scaffolds.</td>
		</tr>
		<tr>
			<td>Dextran</td>
			<td>Sigma Aldrich</td>
			<td>D1037</td>
			<td>MW 500 kDa. This material is no longer being produced by Sigma Aldrich. Alternative suggested is catalog number 31392 (Sigma Aldrich). This material is used to make PD-IPC scaffolds.</td>
		</tr>
		<tr>
			<td>Sodium Bicarbonate&#160;</td>
			<td>Sigma Aldrich</td>
			<td>S5761</td>
			<td>Sodium bicarbonate must be slowly added to the pullulan-dextran polysaccharide solution. Rapid addition of sodium bicarbonate will result in precipitation.&#160;</td>
		</tr>
		<tr>
			<td>Sodium Trimetaphosphate</td>
			<td>Sigma Aldrich</td>
			<td>T5508</td>
			<td>This chemical is hygroscopic and must be stored in the dehumidifying cabinet. Aqueous solution of sodium trimetaphosphate must always be made fresh.</td>
		</tr>
		<tr>
			<td>Sodium Hydroxide</td>
			<td>Sigma Aldrich</td>
			<td>S5881</td>
			<td>This material is hazardous and must be handled with proper protective equipment such as nitrile gloves.</td>
		</tr>
		<tr>
			<td>Chitosan</td>
			<td>Sigma Aldrich</td>
			<td>448877</td>
			<td>MW 190-310 kDa. Acetylation degree of 75 to 85%. Purification of chitosan is required to create stable IPC fibers.</td>
		</tr>
		<tr>
			<td>Acetic Acid</td>
			<td>Merck</td>
			<td></td>
			<td>This can be replaced by another brand type. This material is corrosive and flammable. Protective equipment such as face shield, nitrile gloves, lab coat and shoe cover must be worn when handling this chemical in the fume hood.&#160;</td>
		</tr>
		<tr>
			<td>Alginic acid sodium salt from brown algae, low viscosity</td>
			<td>Sigma Aldrich</td>
			<td>A2158</td>
			<td>Dissolve in water overnight. Filter through sterile 0.2&#181;m syringe filter before use. Store at 4 &#176;C.</td>
		</tr>
		<tr>
			<td>Bovine Serum Albumin</td>
			<td>Sinopharm Chemical Reagent</td>
			<td></td>
			<td>Dissolve in sterile PBS and filter using 0.2 &#181;m syringe filter before use.&#160;</td>
		</tr>
		<tr>
			<td>BCA assay kit</td>
			<td>Pierce</td>
			<td>23225</td>
			<td>This kit was used to measure BSA release from PD-IPC scaffolds.&#160;</td>
		</tr>
		<tr>
			<td>Human Recombinant Vascular Endothelial Growth Factor</td>
			<td>R&#38;D systems</td>
			<td>293-VE</td>
			<td>Dissolve growth factor in 0.2% heparin solution to a final concentration of 5 mg/ml.</td>
		</tr>
		<tr>
			<td>Heparin Sodium Salt From Porcine</td>
			<td>Sigma Aldrich</td>
			<td>H3393</td>
			<td>This can be replaced by another brand type. Dissolve heparin salt in sterile water at a final concentration of 1% and filter through 0.2 &#181;m syringe filter before use.&#160;</td>
		</tr>
		<tr>
			<td>Human Umbilical Vein Endothelial Cells (HUVEC)</td>
			<td>Lonza</td>
			<td>C2517A</td>
			<td>This primary cell type was used in the assay to determine VEGF bioactivity after release from PD-IPC scaffolds.&#160;</td>
		</tr>
		<tr>
			<td>Alamar blue</td>
			<td>Life Technologies</td>
			<td>DAL1025</td>
			<td>This is used to measure cell metabolic activity. Incubate Alamar blue with cells and maintain in standard cell culture conditions for 2 to 4 hours. Measure absorbance at 570 nm to determine Alamar blue percent reduction, which is correlated to the cell activity.&#160;</td>
		</tr>
		<tr>
			<td>ScanVac Coolsafe Lyophilizer</td>
			<td>Labogene</td>
			<td>7.001.200.060</td>
			<td>This is a non-programmable freeze dryer that operates at -105 to -110 &#176;C, This can be replaced by other standard lab lyophilizers.</td>
		</tr>
		<tr>
			<td>Polycaprolactone (PCL)</td>
			<td>Sigma Aldrich</td>
			<td>181609</td>
			<td>MW 65 kDa. This is no longer being manufactured by Sigma Aldrich. This can be replaced by Sigma Aldrich catalog number 704105.</td>
		</tr>
		<tr>
			<td>Dichloromethane</td>
			<td>Sigma Aldrich</td>
			<td>V800151</td>
			<td>This can be replaced by another brand type. This material is hazardous and must be handled in the fume hood. Protective equipment must be worn at all times when handling this chemical.</td>
		</tr>
		<tr>
			<td>Polydimethylsiloxane (PDMS; 184 Silicone Elastomer Kit)</td>
			<td>Dow Corning</td>
			<td>(240)4019862</td>
			<td>The elastomer kit comes with polymer base and crosslinker. Mixing the polymer base and crosslinker in different ratios will result in different stiffness of the PDMS.</td>
		</tr>
		<tr>
			<td>Human Recombinant Beta-Nerve Growth Factor (NGF)</td>
			<td>R&#38;D systems</td>
			<td>256-GF</td>
			<td>Reconstituted in sterile DI water to a final concentration of 100 &#181;g/ml. Aliquot and store in -20 &#176;C until use.</td>
		</tr>
		<tr>
			<td>Human Mesenchymal Stem Cells (hMSC)</td>
			<td>Cambrex</td>
			<td></td>
			<td>This cell type was used in the assay to determine synergistic effect of NGF and nanotopography.</td>
		</tr>
		<tr>
			<td>Rat PC12 Pheochromocytoma Cells&#160;</td>
			<td>ATCC</td>
			<td></td>
			<td>This cell type was used in the neurite outgrowth assay to determine bioactivity of NGF. After exposure to release media with NGF, measure number of cells with neurite extensions and normalize to total number of cells.</td>
		</tr>
		<tr>
			<td>Grade 93 filter paper</td>
			<td>Whatman</td>
			<td>Z699675</td>
			<td>This is used for the purification of chitosan after its precipitation with sodium hydroxide at pH 7.</td>
		</tr>
		<tr>
			<td>Swing bucket centrifuge</td>
			<td>Eppendorf</td>
			<td>5810R</td>
			<td>To be used during the purification of chitosan using 1200 x g speed.&#160;</td>
		</tr>
		<tr>
			<td>Motor with mandrel rotating at constant speed</td>
			<td>Rhymebus</td>
			<td>RM5E</td>
			<td>The motor is used for the fabrication of IPC fibers on pullulan or PCL frame.</td>
		</tr>
		<tr>
			<td>Phosphate buffered saline</td>
			<td>FirstBase</td>
			<td></td>
			<td>Sterilize through filtration (0.2 &#181;m filter) and autoclave.&#160;</td>
		</tr>
		<tr>
			<td>10-mm diameter Tissue Culture Polystyrene Dish (TCPS)</td>
			<td>Greiner</td>
			<td></td>
			<td>The TCPS dish is used for casting of pullulan frame.&#160;</td>
		</tr>
		<tr>
			<td>Human VEGF ELISA kit</td>
			<td>R&#38;D systems</td>
			<td>DVE00</td>
			<td>The ELISA kit is used for detection of VEGF in the release medium.</td>
		</tr>
		<tr>
			<td>Human NGF ELISA kit</td>
			<td>R&#38;D systems</td>
			<td>DY256</td>
			<td>&#160;The ELISA kit is used for detection of NGF in the release medium.</td>
		</tr>
		<tr>
			<td>Plastic Coated Adhesive Tape</td>
			<td>Bel-Art</td>
			<td>9040336</td>
			<td>The adhesive tape is used to securely stick the alligator clip to the rotating mandrel</td>
		</tr>
	</tbody>
</table>

composite scaffolds of interfacial polyelectrolyte fibers for temporally controlled release of biomolecules

Various scaffolds used in tissue engineering require a controlled biochemical environment to mimic the physiological cell niche. Interfacial polyelectrolyte complexation (IPC) fibers can be used for controlled delivery of various biological agents such as small molecule drugs, cells, proteins and growth factors. The simplicity of the methodology in making IPC fibers gives flexibility in its application for controlled biomolecule delivery. Here, we describe a method of incorporating IPC fibers into two different polymeric scaffolds, hydrophilic polysaccharide and hydrophobic polycaprolactone, to create a multi-component composite scaffold. We showed that IPC fibers can be easily embedded into these polymeric structures, enhancing the capability for sustained release and improved preservation of biomolecules. We also created a composite polymeric scaffold with topographical cues and sustained biochemical release that can have synergistic effects on cell behavior. Composite polymeric scaffolds with IPC fibers represent a novel and simple method of recreating the cellular niche.

في هذه المقالة، سعينا إلى إنشاء السقالات المركبة مع الألياف IPC لالاستمرار في اطلاق سراح العديد من الجزيئات الحيوية. تم العثور على خصائص الجزيئات الحيوية المستخدمة في هذه الدراسة في الجدول 1. كان جزءا لا يتجزأ من الألياف IPC أولا إلى PD هيدروجيل ماء لإنشاء سقالة...

Watch this Scientific Journal Video about Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules at JoVE.com

Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules

Scaffolds for tissue engineering need to recapitulate the complex biochemical and biophysical microenvironment of the cellular niche. Here, we show the use of interfacial polyelectrolyte complexation fibers as a platform to create composite, multi-component polymeric scaffolds with sustained biochemical release.

السقالات المركبة من ألياف بينية متضاعف الكتروليتي عن الإصدار التحكم وزمانيا الجزيئات الحيوية

Various scaffolds used in tissue engineering require a controlled biochemical environment to mimic the physiological cell niche. Interfacial ...

composite-scaffolds-interfacial-polyelectrolyte-fibers-for-temporally

Research

JoVE Journal

Bioengineering

8.3K Views.  National University of Singapore. Scaffolds for tissue engineering need to recapitulate the complex biochemical and biophysical microenvironment of the cellular niche. Here, we show the use of interfacial polyelectrolyte complexation fibers as a platform to create composite, multi-component polymeric scaffolds with sustained biochemical release.

Video: Composite Scaffolds of Interfacial Polyelectrolyte Fibers for Temporally Controlled Release of Biomolecules

Elastomeric PGS Scaffolds in Arterial Tissue Engineering

Cardiovascular disease is one of the leading cause of mortality in the US and especially, coronary artery disease increases with an aging population and increasing obesity1. Currently, bypass surgery using autologous vessels, allografts, and synthetic grafts are known as a commonly used for arterial substitutes2. However, these grafts have limited applications when an inner diameter of arteries is less than 6 mm due to low availability, thrombotic complications, compliance mismatch, and late intimal hyperplasia3,4. To overcome these limitations, tissue engineering has been successfully applied as a promising alternative to develop small-diameter arterial constructs that are nonthrombogenic, robust, and compliant. Several previous studies have developed small-diameter arterial constructs with tri-lamellar structure, excellent mechanical properties and burst pressure comparable to native arteries5,6. While high tensile strength and burst pressure by increasing collagen production from a rigid material or cell sheet scaffold, these constructs still had low elastin production and compliance, which is a major problem to cause graft failure after implantation. Considering these issues, we hypothesized that an elastometric biomaterial combined with mechanical conditioning would provide elasticity and conduct mechanical signals more efficiently to vascular cells, which increase extracellular matrix production and support cellular orientation.
The objective of this report is to introduce a fabrication technique of porous tubular scaffolds and a dynamic mechanical conditioning for applying them to arterial tissue engineering. We used a biodegradable elastomer, poly (glycerol sebacate) (PGS)7 for fabricating porous tubular scaffolds from the salt fusion method. Adult primary baboon smooth muscle cells (SMCs) were seeded on the lumen of scaffolds, which cultured in our designed pulsatile flow bioreactor for 3 weeks. PGS scaffolds had consistent thickness and randomly distributed macro- and micro-pores. Mechanical conditioning from pulsatile flow bioreactor supported SMC orientation and enhanced ECM production in scaffolds. These results suggest that elastomeric scaffolds and mechanical conditioning of bioreactor culture may be a promising method for arterial tissue engineering.

Elastomeric PGS scaffolds with vascular smooth muscle cells cultured in a pulsatile flow bioreactor may lead to promising small-diameter arterial constructs with native ECM production in a relatively short culture period.

PGS السقالات المرنة في هندسة الأنسجة الشرياني

Cardiovascular disease is one of the leading cause of mortality in the US and especially, coronary artery disease increases with an aging population and ...

Preparation of 3D Fibrin Scaffolds for Stem Cell Culture Applications

Stem cells are found in naturally occurring 3D microenvironments in vivo, which are often referred to as the stem cell niche 1. Culturing stem cells inside of 3D biomaterial scaffolds provides a way to accurately mimic these microenvironments, providing an advantage over traditional 2D culture methods using polystyrene as well as a method for engineering replacement tissues 2. While 2D tissue culture polystrene has been used for the majority of cell culture experiments, 3D biomaterial scaffolds can more closely replicate the microenvironments found in vivo by enabling more accurate establishment of cell polarity in the environment and possessing biochemical and mechanical properties similar to soft tissue.3 A variety of naturally derived and synthetic biomaterial scaffolds have been investigated as 3D environments for supporting stem cell growth. While synthetic scaffolds can be synthesized to have a greater range of mechanical and chemical properties and often have greater reproducibility, natural biomaterials are often composed of proteins and polysaccharides found in the extracelluar matrix and as a result contain binding sites for cell adhesion and readily support cell culture. Fibrin scaffolds, produced by polymerizing the protein fibrinogen obtained from plasma, have been widely investigated for a variety of tissue engineering applications both in vitro and in vivo 4. Such scaffolds can be modified using a variety of methods to incorporate controlled release systems for delivering therapeutic factors 5. Previous work has shown that such scaffolds can be used to successfully culture embryonic stem cells and this scaffold-based culture system can be used to screen the effects of various growth factors on the differentiation of the stem cells seeded inside 6,7.
 This protocol details the process of polymerizing fibrin scaffolds from fibrinogen solutions using the enzymatic activity of thrombin. The process takes 2 days to complete, including an overnight dialysis step for the fibrinogen solution to remove citrates that inhibit polymerization. These detailed methods rely on fibrinogen concentrations determined to be optimal for embryonic and induced pluripotent stem cell culture. Other groups have further investigated fibrin scaffolds for a wide range of cell types and applications - demonstrating the versatility of this approach 8-12.

This work details the preparation of 3D fibrin scaffolds for culturing and differentiating plutipotent stem cells. Such scaffolds can be used to screen the effects of various biological compounds on stem cell behavior as well as modified to contain drug delivery systems.

إعداد الفايبرين 3D السقالات لتطبيقات الجذعية زراعة الخلايا

Stem cells are found in naturally occurring 3D microenvironments in vivo, which are often referred to as the stem cell niche 1. Culturing stem cells ...

Non-contact, Label-free Monitoring of Cells and Extracellular Matrix using Raman Spectroscopy

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, currently available routine methods require processing steps and alter sample integrity. Raman spectroscopy is a fast method that enables the measurement of biological samples without the need for further processing steps. This laser-based technology detects the inelastic scattering of monochromatic light.6 As every chemical vibration is assigned to a specific Raman band (wavenumber in cm-1), each biological sample features a typical spectral pattern due to their inherent biochemical composition.7-9 Within Raman spectra, the peak intensities correlate with the amount of the present molecular bonds.1 Similarities and differences of the spectral data sets can be detected by employing a multivariate analysis (e.g. principal component analysis (PCA)).10
Here, we perform Raman spectroscopy of living cells and native tissues. Cells are either seeded on glass bottom dishes or kept in suspension under normal cell culture conditions (37 &deg;C, 5% CO2) before measurement. Native tissues are dissected and stored in phosphate buffered saline (PBS) at 4 &deg;C prior measurements. Depending on our experimental set up, we then either focused on the cell nucleus or extracellular matrix (ECM) proteins such as elastin and collagen. For all studies, a minimum of 30 cells or 30 random points of interest within the ECM are measured. Data processing steps included background subtraction and normalization.

Raman spectroscopy is a suitable technique for the non-contact, label-free analysis of living cells, tissue-engineered constructs and native tissues. Source-specific spectral fingerprints can be generated and analyzed using multivariate analysis.

عدم الاتصال، تسمية خالية من رصد خلايا المصفوفة خارج الخلية، وباستخدام التحليل الطيفي رامان

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, ...

Preparation of Light-responsive Membranes by a Combined Surface Grafting and Postmodification Process

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is presented. The polymerization from the membrane surface is induced by plasma treatment of the membrane, followed by reacting the membrane surface with a methanolic solution of 2-hydroxyethyl methacrylate (HEMA). Special attention is given to the process parameters for the plasma treatment prior to the polymerization on the surface. For example, the influence of the plasma-treatment on different types of membranes (e.g.&#160;polyester, polycarbonate, polyvinylidene fluoride) is studied. Furthermore, the time-dependent stability of the surface-grafted membranes is shown by contact angle measurements. When grafting poly(2-hydroxyethyl methacrylate) (PHEMA) in this way, the surface can be further modified by esterification of the alcohol moiety of the polymer with a carboxylic acid function of the desired substance. These reactions can therefore be used for the functionalization of the membrane surface. For example, the surface tension of the membrane can be changed or a desired functionality as the presented light-responsiveness can be inserted. This is demonstrated by reacting PHEMA with a carboxylic acid functionalized spirobenzopyran unit which leads to a light-responsive membrane. The choice of solvent plays a major role in the postmodification step and is discussed in more detail in this paper. The permeability measurements of such functionalized membranes are performed using a Franz cell with an external light source. By changing the wavelength of the light from the visible to the UV-range, a change of permeability of aqueous caffeine solutions is observed.

A plasma-induced polymerization procedure is described for the surface-initiated polymerization on polymer membranes. Further postmodification of the grafted polymer with photochromic substances is presented with a protocol of conducting permeability measurements of light-responsive membranes.

إعداد الأغشية ضوء استجابة من قبل التطعيم سطح الجامع وعملية Postmodification

In order to modify the surface tension of commercial available track-edged polymer membranes, a procedure of surface-initiated polymerization is ...

Alternating Magnetic Field-Responsive Hybrid Gelatin Microgels for Controlled Drug Release

Magnetically-responsive nano/micro-engineered biomaterials that enable a tightly controlled, on-demand drug delivery have been developed as new types of smart soft devices for biomedical applications. Although a number of magnetically-responsive drug delivery systems have demonstrated efficacies through either in vitro proof of concept studies or in vivo preclinical applications, their use in clinical settings is still limited by their insufficient biocompatibility or biodegradability. Additionally, many of the existing platforms rely on sophisticated techniques for their fabrications. We recently demonstrated the fabrication of biodegradable, gelatin-based thermo-responsive microgel by physically entrapping poly(N-isopropylacrylamide-co-acrylamide) chains as a minor component within a three-dimensional gelatin network. In this study, we present a facile method to fabricate a biodegradable drug release platform that enables a magneto-thermally triggered drug release. This was achieved by incorporating superparamagnetic iron oxide nanoparticles and thermo-responsive polymers within gelatin-based colloidal microgels, in conjunction with an alternating magnetic field application system.

We present a facile method to fabricate a biodegradable gelatin-based drug release platform that is magneto-thermally responsive. This was achieved by incorporating superparamagnetic iron oxide nanoparticles and poly(N-isopropylacrylamide-co-acrylamide) within a spherical gelatin micro-network crosslinked by genipin, in conjunction with an alternating magnetic field application system.

بالتناوب المغناطيسي Microgels الجيلاتين الهجين-الميدان الاستجابة لرقابة الإصدار المخدرات

Magnetically-responsive nano/micro-engineered biomaterials that enable a tightly controlled, on-demand drug delivery have been developed as new types of ...

Generation of ESC-derived Mouse Airway Epithelial Cells Using Decellularized Lung Scaffolds

Lung lineage differentiation requires integration of complex environmental cues that include growth factor signaling, cell-cell interactions and cell-matrix interactions. Due to this complexity, recapitulation of lung development in vitro to promote differentiation of stem cells to lung epithelial cells has been challenging. In this protocol, decellularized lung scaffolds are used to mimic the 3-dimensional environment of the lung and generate stem cell-derived airway epithelial cells. Mouse embryonic stem cell are first differentiated to the endoderm lineage using an embryoid body (EB) culture method with activin A. Endoderm cells are then seeded onto decellularized scaffolds and cultured at air-liquid interface for up to 21 days. This technique promotes differentiation of seeded cells to functional airway epithelial cells (ciliated cells, club cells, and basal cells) without additional growth factor supplementation. This culture setup is defined, serum-free, inexpensive, and reproducible. Although there is limited contamination from non-lung endoderm lineages in culture, this protocol only generates airway epithelial populations and does not give rise to alveolar epithelial cells. Airway epithelia generated with this protocol can be used to study cell-matrix interactions during lung organogenesis and for disease modeling or drug-discovery platforms of airway-related pathologies such as cystic fibrosis.

This protocol efficiently directs mouse embryonic stem cell-derived definitive endoderm to mature airway epithelial cells. This differentiation technique uses 3-dimensional decellularized lung scaffolds to direct lung lineage specification, in a defined, serum-free culture setting.

جيل من خلايا الفأر مجرى الهواء طلائي المشتقة ESC عن طريق Decellularized الرئة السقالات

Lung lineage differentiation requires integration of complex environmental cues that include growth factor signaling, cell-cell interactions and ...

Polyelectrolyte Complex for Heparin Binding Domain Osteogenic Growth Factor Delivery

During reconstructive bone surgeries, supraphysiological amounts of growth factors are empirically loaded onto scaffolds to promote successful bone fusion. Large doses of highly potent biological agents are required due to growth factor instability as a result of rapid enzymatic degradation as well as carrier inefficiencies in localizing sufficient amounts of growth factor at implant sites. Hence, strategies that prolong the stability of growth factors such as BMP-2/NELL-1, and control their release could actually lower their efficacious dose and thus reduce the need for larger doses during future bone regeneration surgeries. This in turn will reduce side effects and growth factor costs. Self-assembled PECs have been fabricated to provide better control of BMP-2/NELL-1 delivery via heparin binding and further potentiate growth factor bioactivity by enhancing in vivo stability. Here we illustrate the simplicity of PEC fabrication which aids in the delivery of a variety of growth factors during reconstructive bone surgeries.

Self-assembled polyelectrolyte complexes (PEC) fabricated from heparin and protamine were deposited on alginate beads to entrap and regulate the release of osteogenic growth factors. This delivery strategy enables a 20-fold reduction of BMP-2 dose in spinal fusion applications. This article illustrates the benefits and fabrication of PECs.

مجمع متضاعف الكتروليتي للهيبارين ربط تسليم عظمية عامل نمو المجال

During reconstructive bone surgeries, supraphysiological amounts of growth factors are empirically loaded onto scaffolds to promote successful bone ...

Preparation of Extracellular Matrix Protein Fibers for Brillouin Spectroscopy

Brillouin spectroscopy is an emerging technique in the biomedical field. It probes the mechanical properties of a sample through the interaction of visible light with thermally induced acoustic waves or phonons propagating at a speed of a few km/sec. Information on the elasticity and structure of the material is obtained in a nondestructive contactless manner, hence opening the way to in vivo applications and potential diagnosis of pathology. This work describes the application of Brillouin spectroscopy to the study of biomechanics in elastin and trypsin-digested type I collagen fibers of the extracellular matrix. Fibrous proteins of the extracellular matrix are the building blocks of biological tissues and investigating their mechanical and physical behavior is key to establishing structure-function relationships in normal tissues and the changes which occur in disease. The procedures of sample preparation followed by measurement of Brillouin spectra using a reflective substrate are presented together with details of the optical system and methods of spectral data analysis.

We present a protocol for the application of Brillouin light scattering spectroscopy to elastin and trypsin-purified type I collagen fibers of the extracellular matrix to extract their full elastic properties.

إعداد ألياف البروتين خارج الخلية مصفوفة لBrillouin الطيفي

Brillouin spectroscopy is an emerging technique in the biomedical field. It probes the mechanical properties of a sample through the interaction of ...

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.

المغناطيسي الحساسة والحرارية بولي (<em&gt; N</em&gt; -isopropylacrylamide) ميكروجيلز المستندة إلى مغناطيسيا تسيطر عليها الإصدار

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

Fabrication of Decellularized Cartilage-derived Matrix Scaffolds

Osteochondral defects lack sufficient intrinsic repair capacity to regenerate functionally sound bone and cartilage tissue. To this extent, cartilage research has focused on the development of regenerative scaffolds. This article describes the development of scaffolds that are completely derived from natural cartilage extracellular matrix, coming from an equine donor. Potential applications of the scaffolds include producing allografts for cartilage repair, serving as a scaffold for osteochondral tissue engineering, and providing in vitro models to study tissue formation. By decellularizing the tissue, the donor cells are removed, but many of the natural bioactive cues are thought to be retained. The main advantage of using such a natural scaffold in comparison to a synthetically produced scaffold is that no further functionalization of polymers is required to drive osteochondral tissue regeneration. The cartilage-derived matrix scaffolds can be used for bone and cartilage tissue regeneration in both in vivo and in vitro settings.

Decellularized cartilage-derived scaffolds can be used as a scaffold to guide cartilage repair and as a means to regenerate osteochondral tissue. This paper describes the decellularization process in detail and provides suggestions to use these scaffolds in in vitro settings.

تصنيع السقالات مصفوفة ديسيلولاريزيد المستمدة من الغضروف

Osteochondral defects lack sufficient intrinsic repair capacity to regenerate functionally sound bone and cartilage tissue. To this extent, cartilage ...