이 작품은 화학의 부서 및 연구의 사무실 (RCAP 13-8032)에서 내부 지원을 포함하여 과학 및 공학, 웨스턴 켄터키 대학의 오그 덴 대학에서 지원하고있다. WKU 현미경 시설에서 닥터 존 Andersland (SEM 이미지) 및 연소 공학 (BET 분석)에 대한 WKU 연구소의 부교수 연의 카오의 지원은이 작업을 수행의 중심이되고있다.

에멀젼 1. 준비 <ol><li> 에멀젼 내용 <ol><li> 질량 소금 적당량 0.03 M 용액 10 ㎖를 제조한다. 백금 (IV) 클로라이드 측정 0.101 g, 아연 (II) 클로라이드 (ZnCl 2) 측정 값 0.032 g 및 염화나트륨 0.018 g위한 계수. </li><li> 각각의 시험관에, DI 물 10 ㎖로 각각의 염을 용해. 나중에 사용하기 위해 따로 설정합니다. </li><li> 이 절차를 통해 내용에 대한 20 ml의 밀봉 유리 병을 사용합니다. 유리 병에 균형을 용기. </li><li> 천천히 교반로드 이상과 제로화 규모에 휴식 유리 병으로 그것을 부어 비닐 말단 폴리 디메틸 실록산의 무게. (1.080 ml의에 해당) 1.02 g을 달아. 참고 :이 폴리머의 높은 점도 피펫 비현실적 있습니다. </li><li> 피펫 유리 병에 n- 헵탄 1.02 ml의. 유리 병에 비 이온 계면 활성제 (소르 비탄 모노 올레 에이트) 2 방울을 추가합니다. 피펫 염 용액 0.3 ㎖의 유리 병에 DI-물 0.45 ml의. </li><li> 단단히에서 뚜껑을 돌려서 유리 병을 밀봉합니다. 초음파 처리를 시작하기 전에 유제를 개시하기 위해 60 초 동안 격렬하게 흔들어. </li></ol></li><li> 물 목욕 초음파 처리 장치의 건설 <ol><li> 최소 적재 선에 물 위로 초음파기를 입력합니다. 400 mL의 비커에 수돗물의 250 ML을 추가합니다. 수위가 단지 림이되도록 얼음과 400 mL의 비커를 입력합니다. </li><li> 물 목욕 초음파 처리기 내부에이 비커를 놓습니다. 초음파기에 필 온라인, 필요한 경우 조정을 확인합니다. 링이 물에 목욕 초음파기 바로 옆에 서 놓습니다. </li><li> 팔이 밖으로 확장 될 수 있도록 두 개의 링, 클램프 스탠드를 배치하여, 링에 수직 스탠드하고 얼음 물이 가득 비커에 아래쪽을 가리 키도록 다른 하나는 물 목욕으로 확장됩니다. 온도가 초음파 통하여 모니터 할 수 있도록 또 다른 클램프 링 다운 400 ㎖의 비이커에 온도계를 부착 스탠드. </li></ol></li><li> Emulsif확인해 주시죠 절차 <ol><li> 완전히 비커에 아래로 돌출 클램프로 고정하여 400 mL의 비커에 빠져​​들도록 에멀젼 함유 병을 놓습니다. </li><li> PDMS를 함유하는 혼합물을 유리 바이알은 마찰로 인한 열을 제거하기 위해 비이커의 측면을 건드리지되지 않는다는 것을 보장한다. </li><li> 초음파기를 켜고 7 분간 초음파 시간을 설정합니다. 에멀젼은 매우 열 민감하기 때문에, 비커 내의 온도가 0 ° C에서 5 사이에 걸쳐 초음파인지 확인. 비커 내의 온도가 바람직하다 일단 초음파를 시작한다. </li><li> 초음파의 7 분 후, 에멀젼에 형성 수있는 덩어리를 제거하기 위해 유리 병의 상단을 잡고, 1 분 / 소용돌이를 흔들 부드럽게 병을 제거하고. </li><li> 비커의 내용을 폐기하십시오. 물 250 ㎖로 채우고 내에서 1cm로 채우기에 비커의 상단을 얼음을 추가합니다. </li><li> 다시 클램프의 병을 놓습니다. resum하기 위해 얼음 물 아래 잠수함7 분 동안 전자 초음파. </li><li> 반복 여덟, 7 분간 초음파 처리 기간의 총 1.3.6 1.3.3하는 단계, 또는 초음파 균질 것으로 나타나고 더 덩어리가 존재하지 않을 때까지. 실온에서 보관하십시오. 주 : 유화 며칠 동안 안정해야하지만 균일 나타날 때까지 7 분 간격으로 상기와 같이 초음파에 의해 회수 될 수있다. 실온에서 보관하십시오. </li></ol></li></ol> 2. 교차 결합 <ol><li> 트리에 톡시 실란 / 계면 활성제 용액을 첨가 설치 프로그램 <ol><li> 피펫 5.4 ml를 시험관에 톡시 실란. 나중에 사용하기 위해 후드 테스트 튜브 랙에 놓는다. </li><li> 얼음 물 400 mL의 비커를 입력하고 후드 아래에 배치합니다. 다음 링이 부착 된 클램프 스탠드 400 mL의 비커 장소에, 비커의 입구에 직접 확장. 이 트리에 톡시 실란의 추가를위한 얼음 욕조됩니다. </li><li> 링 스탠드의 반대편에 핫 플레이트를 놓습니다. 약 700 ml의 800 비이커를 채우수돗물. 핫 플레이트에 놓습니다. </li><li> 핫 플레이트의 전원을 켜고 800 mL의 비커 내부에 85 ° C 75의 온도를 유지한다. 800 ㎖의 비이커 안에 물의 온도가 모니터링 될 수 있도록 링 스탠드에 온도계를 부착 클램프. </li><li> 물 375 ㎖ (4.62 mM)을로 도데 실 황산나트륨 0.5 g을 용해시킴으로써 계면 활성제 용액을 생성한다. 깨끗하고 빈 시험관에 계면 활성제 용액의 약 10 ML을 추가합니다. </li><li> 다른 링 클램프 활성제 시험관과 후드 아래 스탠드 부착은 액체 레벨이 800 ㎖의 비커 안에서 수면 아래가되도록 고정. 열 평형 10 분을 허용합니다. </li><li> 여과지를 적시고 작은 깔때기의 상단에 배치. 250 ㎖의 삼각 플라스크 내부의 깔때기의 줄기를 놓고 후드 아래에 플라스크를 배치합니다. </li></ol></li><li> 트리에 톡시 실란의 추가 <ol><li> 빙수 부리 위에 클램프 에멀젼 바이알을 놓고후드 안쪽 어. 바이알 내용물이 물의 표면 아래에 있도록 클램프 PDMS 혼합물을 위치. 트리에 톡시 실란의 첨가는 발열 반응을 초래하므로 에멀젼은 구조를 유지하기 위하여 저온 유지되어야한다. </li><li> 가스 축적을 방지하는 데 유리 바이알에서 뚜껑을 제거한다. </li><li> 천천히 약 10 초 (약 0.5 ㎖ / 초)에 걸쳐 연속적인 스트림으로 유리 바이알에 시험관 함유 트리에 톡시 실란을 붓는다. 주의 : 트리에 톡시 실란의 첨가는 발열 반응과 부식성 염화수소 가스의 방출을 개시한다. 유리 병은 매우 뜨거워 질 것이고, 독성 가스 혼합물로부터 진화 할 것이다. 트리에 톡시 실란을 추가하는 동안 내용을 저어하지 마십시오. </li><li> 열 보호 장갑을 착용 한 채 완전히 트리에 톡시 실란을 추가 한 후, 부드럽게 유리 교반 막대와 내용을 저어. 2 분 동안 또는 유리 병에서 진화 가스 멈출 때까지 기다립니다. </li><li> FOLL가교 때문에, 시료에서 볼 상분리 없다. 덩어리가 존재하는 경우, 바이알을 밀봉하고 뚜껑으로 병 채 20 초 동안 흔들어 엄격. </li></ol></li><li> 구슬 생산 <ol><li> 유리 병에서 가교 유화를 그릴 청소, 유리 파스퇴르 피펫을 사용합니다. 적가 시험관 방울 사이에 가능한 한 적은 시간이 소요로 (75 및 85 ° C 사이에서 유지되어야한다), 계면 활성제 용액에 가교 된 에멀젼을 추가한다. </li><li> 30 초 에멀젼의 첨가 후 1 분 고체 시험관 내부에 형성되기 시작으로, 계면 활성제 용액을 천천히 가스를 포한한다. </li><li> 열 보호 장갑을 착용하고있는 동안, 클램프에서 테스트 튜브를 타고 후드 아래 여과 장치에 전체 내용을 붓는다. 5 분 동안 필터. 필터에서 필터 용지를 제거합니다. </li><li> H 하에서 O / N의 건조 시계 유리 비드 상에 분리 된 고체를 여과를 전송할짐 우드. 구슬의 청소는 무기한 연기 될 수있다. 상점은 필요할 때까지 밀폐 된 유리 병에 실온에서 구슬을 건조하고 깨끗한 즉시 사용하기 전에. </li></ol></li><li> 구슬 청소 <ol><li> 후드 아래 다른 여과 장치를 만들고 필터 종이 위에 깔때기 내부의 건조 구슬을 배치합니다. </li><li> 모든 구슬이 세척되어 있는지 확인하기 위해 주위에 약간을 이동, 부드럽게 구슬을 씻어 DI-물이 가득 플라스틱 세척 병을 사용합니다. </li><li> 구슬은 후드 아래에 시계 접시에 그들을 배치하여 1 시간 동안 건조 시키십시오. 물 세척에 대해 동일한 방법을 사용하여 구슬을 씻어 헥산 가득 세척 병을 사용합니다. </li><li> 시계 유리 구슬을 놓습니다. 시계 접시를 놓고 후드 아래 구슬은 건조. </li><li> 구슬이 완전히 건조 된 후 나중에 사용하기 위해 실온에서 작은 밀폐 유리 병 및 저장에 배치합니다. </li></ol></li><li> SEM 분석 및 SEM 설정의 구슬을 장착 <ol><li> DO의 스트립을 배치구슬이 장착 될에 그루터기 위에 uble 양면 탄소 전도성 테이프. 가위를 사용하여, 가장자리 아무런 테이프 중단 없도록 그루터기 주위 트림. </li><li> 평평한 표면에 스텁에서 필터 종이를 놓습니다. 접착제 밑면이 노출되도록 테이프로부터 상부층을 제거한다. </li><li> 조심스럽게 그루터기 위에 구슬을 붓는다. 일부 구슬 테이프에 충실하지만, 대부분은 필터 종이에 반사되어 토지 것입니다. 그들은 필터 종이에 머물 경우 유리 병에이 다시 부어. 필요한 경우 오염 될 (2.4.5 2.4.2에 따라) 어떤 구슬을 세척, 반복합니다. </li><li> 구슬이 스텁에 안전하게 보장하기 위해, 전구 주사기를 사용하여 가볍게 스텁 표면에 매우 밀접하게 날려. 일부만 테이프에 부착하는 경우 스텁 위에 더 구슬 붓는다. 모든 구슬은 SEM 챔버에 그루터기를 배치하고 대피하기 전에 안전한지 확인합니다. </li><li> 샘플이 제대로 장착되고 나면 그들은 지금 SEM의 항문을받을 준비가되어이 Analysis (15). 비드의 표면 형상의 분해능을 최적화하기 위해 15 keV의 VAC에서 LOW 모드에서 이미지를 수집한다. </li></ol></li></ol>

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H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Surface+modification+for+PDMS-based+microfluidic+devices.">Surface modification for PDMS-based microfluidic devices.</a> Electrophoresis. 33 (1), 89-104 (2012).</li><li>Spietelun, A., Pilarczyk, M., Kloskowski, A., Namie&#347;nik, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Polyethylene+glycol-coated+solid-phase+microextraction+fibres+for+the+extraction+of+polar+analytes&#8212;A+review.">Polyethylene glycol-coated solid-phase microextraction fibres for the extraction of polar analytes&#8212;A review.</a> Talanta. 87, 1-7 (2011).</li><li>Vas, G., V&#233;key, K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Solid-phase+microextraction:+a+powerful+sample+preparation+tool+prior+to+mass+spectrometric+analysis.">Solid-phase microextraction: a powerful sample preparation tool prior to mass spectrometric analysis.</a> J. 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Chem. 46 (1), 21-32 (2007).</li><li>Sun, W., Yan, X., Zhu, X. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Synthesis,+porous+structure,+and+underwater+acoustic+properties+of+macroporous+cross-linked+copolymer+beads.">Synthesis, porous structure, and underwater acoustic properties of macroporous cross-linked copolymer beads.</a> Colloid Polym. Sci. 290 (1), 73-80 (2012).</li><li>Dufaud, O., Favre, E., Sadtler, V. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Porous+elastomeric+beads+from+crosslinked+emulsions.">Porous elastomeric beads from crosslinked emulsions.</a> J. Appl. Polym. Sci. 83 (5), 967-971 (2002).</li><li>Farmer, B. C., Mason, M., Nee, 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=Concave+porosity+non-polar+beads+by+a+modified+microbubble+fabrication.">Concave porosity non-polar beads by a modified microbubble fabrication.</a> Mater. Lett. 98, 105-107 (2013).</li><li>Flegler, S. L., Heckman, J. W., Klomparens, K. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Scanning and Transmission Electron Microscopy: An Introduction. , 151-155 (1995).</li><li>Brunauer, S., Emmett, P. H., Teller, E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Adsorption+of+Gases+in+Multimolecular+Layers.">Adsorption of Gases in Multimolecular Layers.</a> J. Am. Chem. Soc. 60 (2), 309-319 (1938).</li><li>Sing, K. S. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Characterization+of+porous+materials:+past,+present+and+future.">Characterization of porous materials: past, present and future.</a> Colloids Surf. A. 241 (1), 3-7 (2004).</li></ol>

The authors have nothing to disclose.

도 1의 다른 SEM 이미지로도 1a의 비교에 의해 볼 수 있듯이,이 프로토콜을 이용하여 (전해질 농도 및 아이덴티티를 조정함으로써) 생성 된 비드., 낮은 이온 강도 에멀젼 제조 것과는 근본적으로 다르다 당초 보고서 사용 상기 수성 지방족 인터페이스 14 중합 가교 결합 반응을 촉매 의도 PTCL 4. 이 보고서에서, 큰 오목 들여 쓰기는 볼 수 있었다. 해당 보고서...

Polydimethylsiloxane (PDMS) is one of the most widely used silicone compounds. Its biocompatibility has led to widespread use in implant and other biomedical engineering structures1,2. It is trivially cross-linked into elastic structures using an organosilyl compound (such as triethoxysilane), a simple and reliable procedure which has made it useful for cast polymer applications where some flexibility is required3. Once cross-linked, PDMS is largely inert, particularly in biological conditions, and is therefore useful for a variety of food and medical applications4,5. Ease of casting, chemical inertness, and hydrophobicity have made it a natural choice for microfluidic devices6,7. Its affinity for non-halogenated, non-polar organic compounds has made it a popular stationary phase in separations chemistry8-10. 
Recently, microbubble fabrications have been used to generate porous beads for use as catalyst structural substrates or in chemical separations11,12. In both applications, ideal materials will have a maximized surface-area-to-volume (SAV) ratio for best efficiency. In a microbubble fabrication process, microstructuring of materials is typically accomplished by isolating the polymer in aliphatic &#8220;microbubbles&#8221; by emulsification in an aqueous continuous phase. The initial report of microporous PDMS beads produced them by mechanical emulsification of two phases (aliphatic and aqueous)13. The stock PDMS liquid (and its cross-linking agent) is dissolved into the aliphatic phase, which is structured into microscopic beads by being forced to cavitate within the (continuous) aqueous phase. The emulsification is stabilized by the addition of a non-ionic surfactant. When the emulsion is added dropwise to a heated bath, solid beads form by agglomeration of the microbubbles into clusters of tiny spheres of cross-linked PDMS. Our goal in this protocol is to modify this procedure to develop beads with an inverted porosity to improve the SAV ratio of the material.
As reported previously, control of the beads can be directed to some extent by the aliphatic:aqueous ratios in the emulsion. However, we have reported recently that addition of platinum(IV) chloride (PtCl4) inverts the porosity: materials are formed in which the PDMS is riddled with concave pores14. This indicates that the aqueous layer cavitates inside the aliphatic one, despite having similar aliphatic:aqueous ratios to those published in the original work13. The primary advantage of our method is that this concave porosity should naturally result in an increased SAV ratio, and thus, improved efficiency for analytical chemistry applications. While we are continuing to explore the specific effects of the addition of the platinum compound, we show here that the same effect can be accomplished using any aqueously soluble ionic compound, though perhaps to a reduced extent. Because our techniques also differ in some key aspects from what has been previously reported, we present our protocols here as a video to encourage others to extend our methods. Most notably, we use a common bath sonicator of the type used to clean glassware or other equipment, rather than the (considerably more expensive) probe sonicator often used in microbubble fabrication. This adjusted approach to the microbubble fabrication procedure could potentially be extended for the production of large quantities of bulk materials as well, creating porous sheets or slabs which could have applications for biomedical devices, aerospace and automotive industry, or substrates for chemical catalysis. Users seeking to generate high-SAV-ratio, microstructured materials using other similar polymers for such analyses may find that our protocols can be extended to any polymer for which the microbubble emulsion technique can be applied.

<table><tbody><tr><td>Poly(dimethylsiloxane), vinyl terminated</td><td>Sigma-Aldrich</td><td>68083-19-2</td><td></td></tr><tr><td>n-Heptane</td><td>Sigma-Aldrich</td><td>142-82-5</td><td>Flammable</td></tr><tr><td>Triethoxysilane</td><td>Sigma-Aldrich</td><td>998-30-1</td><td>Flammable, Accutely Toxic</td></tr><tr><td>Sorbitan Monoleate (Span-80)</td><td>Fluker</td><td>1338-43-8</td><td></td></tr><tr><td>Platinum(IV) Chloride</td><td>Sigma-Aldrich</td><td>13454-96-1</td><td>Accutely Toxic</td></tr><tr><td>Zinc(II) Chloride</td><td>Sigma-Aldrich</td><td>7646-85-7</td><td></td></tr><tr><td>Sodium Chloride</td><td>Sigma-Aldrich</td><td>7647-14-5</td><td></td></tr><tr><td>2.8 L Water Bath Sonicator</td><td>VWR</td><td>97043-964</td><td></td></tr></tbody></table>

microbubble fabrication of concave-porosity pdms beads

Microbubble fabrication (by use of a fine emulsion) provides a means of increasing the surface-area-to-volume (SAV) ratio of polymer materials, which is particularly useful for separations applications. Porous polydimethylsiloxane (PDMS) beads can be produced by heat-curing such an emulsion, allowing the interface between the aqueous and aliphatic phases to mold the morphology of the polymer. In the procedures described here, both polymer and crosslinker (triethoxysilane) are sonicated together in a cold-bath sonicator. Following a period of cross-linking, emulsions are added dropwise to a hot surfactant solution, allowing the aqueous phase of the emulsion to separate, and forming porous polymer beads. We demonstrate that this method can be tuned, and the SAV ratio optimized, by adjusting the electrolyte content of the aqueous phase in the emulsion. Beads produced in this way are imaged with scanning electron microscopy, and representative SAV ratios are determined using Brunauer&#8211;Emmett&#8211;Teller (BET) analysis. Considerable variability with the electrolyte identity is observed, but the general trend is consistent: there is a maximum in SAV obtained at a specific concentration, after which porosity decreases markedly.

다른 전해질 조건 에멀젼으로부터 발생 비드의 대표적인 SEM 이미지가도 1에 도시된다.도 1a는 DuFaud하여 얻은, 등. (13)과 유사한 비드를 도시 모든 전해질의 첨가없이, 우리의 방법을 사용하여 제조. 구슬은 각각의 금속 이온에 대해 서로 다른 형태 학적 결과, 그림 1B-D에 표시. 도시 된 모든 이미지에 대해, 0.03 - M 전해질 용액 300 μL 그 위상 0.012 M의 전해질 농...

Watch this Scientific Journal Video about Microbubble Fabrication of Concave-porosity PDMS Beads at JoVE.com

Microbubble Fabrication of Concave-porosity PDMS Beads

Procedures used to generate microstructured concave-porosity polydimethylsiloxane beads are presented. Effects of electrolyte concentration and identity within the aqueous phase are particularly emphasized.

오목 다공성 PDMS 비즈의 마이크로 버블 제작

Microbubble fabrication (by use of a fine emulsion) provides a means of increasing the surface-area-to-volume (SAV) ratio of polymer materials, which is ...

microbubble-fabrication-of-concave-porosity-pdms-beads

Research

JoVE Journal

Chemistry

8.3K 조회수.  Western Kentucky University. Procedures used to generate microstructured concave-porosity polydimethylsiloxane beads are presented. Effects of electrolyte concentration and identity within the aqueous phase are particularly emphasized. 

비디오: Microbubble Fabrication of Concave-porosity PDMS Beads

Micropunching Lithography for Generating Micro- and Submicron-patterns on Polymer Substrates

Conducting polymers have attracted great attention since the discovery of high conductivity in doped polyacetylene in 19771. They offer the advantages of low weight, easy tailoring of properties and a wide spectrum of applications2,3. Due to sensitivity of conducting polymers to environmental conditions (e.g., air, oxygen, moisture, high temperature and chemical solutions), lithographic techniques present significant technical challenges when working with these materials4. For example, current photolithographic methods, such as ultra-violet (UV), are unsuitable for patterning the conducting polymers due to the involvement of wet and/or dry etching processes in these methods. In addition, current micro/nanosystems mainly have a planar form5,6. One layer of structures is built on the top surfaces of another layer of fabricated features. Multiple layers of these structures are stacked together to form numerous devices on a common substrate. The sidewall surfaces of the microstructures have not been used in constructing devices. On the other hand, sidewall patterns could be used, for example, to build 3-D circuits, modify fluidic channels and direct horizontal growth of nanowires and nanotubes.
A macropunching method has been applied in the manufacturing industry to create macropatterns in a sheet metal for over a hundred years. Motivated by this approach, we have developed a micropunching lithography method (MPL) to overcome the obstacles of patterning conducting polymers and generating sidewall patterns. Like the macropunching method, the MPL also includes two operations (Fig. 1): (i) cutting; and (ii) drawing. The "cutting" operation was applied to pattern three conducting polymers4, polypyrrole (PPy), Poly(3,4-ethylenedioxythiophen)-poly(4-styrenesulphonate) (PEDOT) and polyaniline (PANI). It was also employed to create Al microstructures7. The fabricated microstructures of conducting polymers have been used as humidity8, chemical8, and glucose sensors9. Combined microstructures of Al and conducting polymers have been employed to fabricate capacitors and various heterojunctions9,10,11. The "cutting" operation was also applied to generate submicron-patterns, such as 100- and 500-nm-wide PPy lines as well as 100-nm-wide Au wires. The "drawing" operation was employed for two applications: (i) produce Au sidewall patterns on high density polyethylene (HDPE) channels which could be used for building 3D microsystems12,13,14, and (ii) fabricate polydimethylsiloxane (PDMS) micropillars on HDPE substrates to increase the contact angle of the channel15.

A micropunching lithography approach is developed to generate micro- and submicron-patterns on top, sidewall and bottom surfaces of polymer substrates. It overcomes the obstacles of patterning conducting polymers and generating sidewall patterns. This method allows rapid fabrication of multiple features and is free of aggressive chemistry.

마이크로 및 Submicron 패턴 폴리머 기판을 생성하기위한 리소그래피를 Micropunching

Conducting polymers have attracted great attention since the discovery of high conductivity in doped polyacetylene in 19771. They offer the advantages of ...

연구

공학

Fabrication of a Microfluidic Device for the Compartmentalization of Neuron Soma and Axons

In this video, we demonstrate the technique of soft lithography with polydimethyl siloxane (PDMS) which we use to fabricate a microfluidic device for culturing neurons. Previously, a silicon wafer was patterned with the design for the neuron microfluidic device using SU-8 and photolithography to create a master mold, or what we simply refer to as a "master". Next, we pour the silicon polymer PDMS on top of the master which is then cured by heating the PDMS to 80&deg;C for 1 hour. The PDMS forms a negative mold of the device. The PDMS is then carefully cut and lifted away from the master. Holes are punched where the reservoirs will be and the excess PDMS trimmed away from the device. Nitrogen is used to blow away any excess debris from the device. At this point the devices are now ready for use and can either bonded to corning No. 1 cover glass with a plasma sterilizer/cleaner or can be reversibly bound to the cover glass by simply placing the device on top of the cover glass. The reversible bonding of the device to glass is covered in a separate video and requires first that the device be sterilized either with 70% ethanol or by autoclaving. Plasma treating sterilizes the devices so no further treatment is necessary. It is, however, important, when plasma-treating the devices, to add liquid to the devices within 10 minutes of the plasma treatment while the surfaces are still hydrophilic. Waiting longer than 10 minutes to add liquid to the device makes it difficult for the liquid to enter the device. The neuron devices are typically plasma-bound to cover glass and 0.5 mg/ml poly-L-lysine (PLL) in pH 8.5 borate buffer is immediately added to the device. After a minimum of 3 hours incubating with PLL, the devices are washed with dH2O water a minimum of 3 times with at least 15 minutes between each wash. Next, the water is removed and fresh media is added to the device. At this point the device is ready for use. It is important to remember at this point to never remove all the media from the device. Always leave media in the main channel.

In this video we demonstrate the technique of soft lithography with polydimethyl siloxane (PDMS) which we use to farbricate a microfluidic device for culturing neurons.

신경 소마와 Axons의 Compartmentalization위한 Microfluidic 장치의 제작

In this video, we demonstrate the technique of soft lithography with polydimethyl siloxane (PDMS) which we use to fabricate a microfluidic device for ...

생물학

Microfluidic Chips Controlled with Elastomeric Microvalve Arrays

Miniaturized microfluidic systems provide simple and effective solutions for low-cost point-of-care diagnostics and high-throughput biomedical assays. Robust flow control and precise fluidic volumes are two critical requirements for these applications. We have developed microfluidic chips featuring elastomeric polydimethylsiloxane (PDMS) microvalve arrays that: 1) need no extra energy source to close the fluidic path, hence the loaded device is highly portable; and 2) allow for microfabricating deep (up to 1 mm) channels with vertical sidewalls and resulting in very precise features.

The PDMS microvalves-based devices consist of three layers: a fluidic layer containing fluidic paths and microchambers of various sizes, a control layer containing the microchannels necessary to actuate the fluidic path with microvalves, and a middle thin PDMS membrane that is bound to the control layer. Fluidic layer and control layers are made by replica molding of PDMS from SU-8 photoresist masters, and the thin PDMS membrane is made by spinning PDMS at specified heights. The control layer is bonded to the thin PDMS membrane after oxygen activation of both, and then assembled with the fluidic layer. The microvalves are closed at rest and can be opened by applying negative pressure (e.g., house vacuum). Microvalve closure and opening are automated via solenoid valves controlled by computer software.

Here, we demonstrate two microvalve-based microfluidic chips for two different applications. The first chip allows for storing and mixing precise sub-nanoliter volumes of aqueous solutions at various mixing ratios. The second chip allows for computer-controlled perfusion of microfluidic cell cultures.

The devices are easy to fabricate and simple to control. Due to the biocompatibility of PDMS, these microchips could have broad applications in miniaturized diagnostic assays as well as basic cell biology studies.

We demonstrate protocols for manufacturing and automating elastomeric polydimethylsiloxane (PDMS)-based microvalve arrays that need no extra energy to close and feature photolithographically defined precise volumes. A parallel subnanoliter-volume mixer and an integrated microfluidic perfusion system are presented.

Microfluidic 칩은 탄성 Microvalve의 배열을 제어

Miniaturized microfluidic systems provide simple and effective solutions for low-cost point-of-care diagnostics and high-throughput biomedical assays.  ...

High Throughput Single-cell and Multiple-cell Micro-encapsulation

Microfluidic encapsulation methods have been previously utilized to capture cells in picoliter-scale aqueous, monodisperse drops, providing confinement from a bulk fluid environment with applications in high throughput screening, cytometry, and mass spectrometry. We describe a method to not only encapsulate single cells, but to repeatedly capture a set number of cells (here we demonstrate one- and two-cell encapsulation) to study both isolation and the interactions between cells in groups of controlled sizes. By combining drop generation techniques with cell and particle ordering, we demonstrate controlled encapsulation of cell-sized particles for efficient, continuous encapsulation. Using an aqueous particle suspension and immiscible fluorocarbon oil, we generate aqueous drops in oil with a flow focusing nozzle. The aqueous flow rate is sufficiently high to create ordering of particles which reach the nozzle at integer multiple frequencies of the drop generation frequency, encapsulating a controlled number of cells in each drop. For representative results, 9.9 &mu;m polystyrene particles are used as cell surrogates. This study shows a single-particle encapsulation efficiency Pk=1 of 83.7% and a double-particle encapsulation efficiency Pk=2 of 79.5% as compared to their respective Poisson efficiencies of 39.3% and 33.3%, respectively. The effect of consistent cell and particle concentration is demonstrated to be of major importance for efficient encapsulation, and dripping to jetting transitions are also addressed. 
Introduction 
Continuous media aqueous cell suspensions share a common fluid environment which allows cells to interact in parallel and also homogenizes the effects of specific cells in measurements from the media. High-throughput encapsulation of cells into picoliter-scale drops confines the samples to protect drops from cross-contamination, enable a measure of cellular diversity within samples, prevent dilution of reagents and expressed biomarkers, and amplify signals from bioreactor products. Drops also provide the ability to re-merge drops into larger aqueous samples or with other drops for intercellular signaling studies.1,2 The reduction in dilution implies stronger detection signals for higher accuracy measurements as well as the ability to reduce potentially costly sample and reagent volumes.3 Encapsulation of cells in drops has been utilized to improve detection of protein expression,4 antibodies,5,6 enzymes,7 and metabolic activity8 for high throughput screening, and could be used to improve high throughput cytometry.9 Additional studies present applications in bio-electrospraying of cell containing drops for mass spectrometry10 and targeted surface cell coatings.11 Some applications, however, have been limited by the lack of ability to control the number of cells encapsulated in drops. Here we present a method of ordered encapsulation12 which increases the demonstrated encapsulation efficiencies for one and two cells and may be extrapolated for encapsulation of a larger number of cells.
To achieve monodisperse drop generation, microfluidic "flow focusing" enables the creation of controllable-size drops of one fluid (an aqueous cell mixture) within another (a continuous oil phase) by using a nozzle at which the streams converge.13 For a given nozzle geometry, the drop generation frequency f and drop size can be altered by adjusting oil and aqueous flow rates Qoil and Qaq. As the flow rates increase, the flows may transition from drop generation to unstable jetting of aqueous fluid from the nozzle.14 
When the aqueous solution contains suspended particles, particles become encapsulated and isolated from one another at the nozzle. For drop generation using a randomly distributed aqueous cell suspension, the average fraction of drops Dk containing k cells is dictated by Poisson statistics, where Dk = &lambda;k exp(-&lambda;)/(k!) and &lambda; is the average number of cells per drop. The fraction of cells which end up in the "correctly" encapsulated drops is calculated using Pk = (k x Dk)/&Sigma;(k' x Dk'). The subtle difference between the two metrics is that Dk relates to the utilization of aqueous fluid and the amount of drop sorting that must be completed following encapsulation, and Pk relates to the utilization of the cell sample. As an example, one could use a dilute cell suspension (low &lambda;) to encapsulate drops where most drops containing cells would contain just one cell. While the efficiency metric Pk would be high, the majority of drops would be empty (low Dk), thus requiring a sorting mechanism to remove empty drops, also reducing throughput.15
Combining drop generation with inertial ordering provides the ability to encapsulate drops with more predictable numbers of cells per drop and higher throughputs than random encapsulation. Inertial focusing was first discovered by Segre and Silberberg16 and refers to the tendency of finite-sized particles to migrate to lateral equilibrium positions in channel flow. Inertial ordering refers to the tendency of the particles and cells to passively organize into equally spaced, staggered, constant velocity trains. Both focusing and ordering require sufficiently high flow rates (high Reynolds number) and particle sizes (high Particle Reynolds number).17,18 Here, the Reynolds number Re =uDh/&nu; and particle Reynolds number Rep =Re(a/Dh)2, where u is a characteristic flow velocity, Dh [=2wh/(w+h)] is the hydraulic diameter, &nu; is the kinematic viscosity, a is the particle diameter, w is the channel width, and h is the channel height. Empirically, the length required to achieve fully ordered trains decreases as Re and Rep increase. Note that the high Re and Rep requirements (for this study on the order of 5 and 0.5, respectively) may conflict with the need to keep aqueous flow rates low to avoid jetting at the drop generation nozzle. Additionally, high flow rates lead to higher shear stresses on cells, which are not addressed in this protocol. The previous ordered encapsulation study demonstrated that over 90% of singly encapsulated HL60 cells under similar flow conditions to those in this study maintained cell membrane integrity.12 However, the effect of the magnitude and time scales of shear stresses will need to be carefully considered when extrapolating to different cell types and flow parameters. The overlapping of the cell ordering, drop generation, and cell viability aqueous flow rate constraints provides an ideal operational regime for controlled encapsulation of single and multiple cells.
Because very few studies address inter-particle train spacing,19,20 determining the spacing is most easily done empirically and will depend on channel geometry, flow rate, particle size, and particle concentration. Nonetheless, the equal lateral spacing between trains implies that cells arrive at predictable, consistent time intervals. When drop generation occurs at the same rate at which ordered cells arrive at the nozzle, the cells become encapsulated within the drop in a controlled manner. This technique has been utilized to encapsulate single cells with throughputs on the order of 15 kHz,12 a significant improvement over previous studies reporting encapsulation rates on the order of 60-160 Hz.4,15 In the controlled encapsulation work, over 80% of drops contained one and only one cell, a significant efficiency improvement over Poisson (random) statistics, which predicts less than 40% efficiency on average.12
In previous controlled encapsulation work,12 the average number of particles per drop &lambda; was tuned to provide single-cell encapsulation. We hypothesize that through tuning of flow rates, we can efficiently encapsulate any number of cells per drop when &lambda; is equal or close to the number of desired cells per drop. While single-cell encapsulation is valuable in determining individual cell responses from stimuli, multiple-cell encapsulation provides information relating to the interaction of controlled numbers and types of cells. Here we present a protocol, representative results using polystyrene microspheres, and discussion for controlled encapsulation of multiple cells using a passive inertial ordering channel and drop generation nozzle.

Combining monodisperse drop generation with inertial ordering of cells and particles, we describe a method to encapsulate a desired number of cells or particles in a single drop at kHz rates. We demonstrate efficiencies twice exceeding those of unordered encapsulation for single- and double-particle drops.

높은 처리량 마이크로 캡슐 단일 셀 및 다중 셀

Microfluidic encapsulation methods have been previously utilized to capture cells in picoliter-scale aqueous, monodisperse drops, providing confinement ...

생체공학

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

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

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

콜로이드 입자의 자기 조립 과정을 통해 PDMS 미세 유체 칩의 하위 50 Nm의 나노 유체 접합 만들기

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

A Microfluidic Technique to Probe Cell Deformability

Here we detail the design, fabrication, and use of a microfluidic device to evaluate the deformability of a large number of individual cells in an efficient manner. Typically, data for ~102 cells can be acquired within a 1 hr experiment. An automated image analysis program enables efficient post-experiment analysis of image data, enabling processing to be complete within a few hours. Our device geometry is unique in that cells must deform through a series of micron-scale constrictions, thereby enabling the initial deformation and time-dependent relaxation of individual cells to be assayed. The applicability of this method to human promyelocytic leukemia (HL-60) cells is demonstrated. Driving cells to deform through micron-scale constrictions using pressure-driven flow, we observe that human promyelocytic (HL-60) cells momentarily occlude the first constriction for a median time of 9.3 msec before passaging more quickly through the subsequent constrictions with a median transit time of 4.0 msec per constriction. By contrast, all-trans retinoic acid-treated (neutrophil-type) HL-60 cells occlude the first constriction for only 4.3 msec before passaging through the subsequent constrictions with a median transit time of 3.3 msec. This method can provide insight into the viscoelastic nature of cells, and ultimately reveal the molecular origins of this behavior.

We demonstrate a microfluidics-based assay to measure the timescale for cells to transit through a sequence of micron-scale constrictions.

미세 유체 기술은 셀 변형능을 검사 할

Here we detail the design, fabrication, and use of a microfluidic device to evaluate the deformability of a large number of individual cells in an ...

Fabrication of Refractive-index-matched Devices for Biomedical Microfluidics

The use of microfluidic devices has emerged as a defining tool for biomedical applications. When combined with modern microscopy techniques, these devices can be implemented as part of a robust platform capable of making simultaneous complementary measurements. The primary challenge created by the combination of these two techniques is the mismatch in refractive index between the materials traditionally used to make microfluidic devices and the aqueous solutions typically used in biomedicine. This mismatch can create optical artifacts near the channel or device edges. One solution is to reduce the refractive index of the material used to fabricate the device by using a fluorinated polymer such as MY133-V2000 whose refractive index is similar to that of water (n = 1.33). Here, the construction of a microfluidic device made out of MY133-V2000 using soft lithography techniques is demonstrated, using O2 plasma in conjunction with an acrylic holder to increase the adhesion between the MY133-V2000 fabricated device and the polydimethylsiloxane (PDMS) substrate. The device is then tested by incubating it filled with cell culture media for 24 h to demonstrate the ability of the device to maintain cell culture conditions during the course of a typical imaging experiment. Finally, quantitative phase microscopy (QPM) is used to measure the distribution of mass within the live adherent cells in the microchannel. This way, the increased precision, enabled by fabricating the device from a low index of refraction polymer such as MY133-V2000 in lieu of traditional soft lithography materials such as PDMS, is demonstrated. Overall, this approach for fabricating microfluidic devices can be readily integrated into existing soft lithography workflows in order to reduce optical artifacts and increase measurement precision.

This protocol describes the fabrication of microfluidic devices from MY133-V2000 to eliminate artifacts that often arise in microchannels due to the mismatching refractive indices between microchannel structures and an aqueous solution. This protocol uses an acrylic holder to compress the encapsulated device, improving adhesion both chemically and mechanically.

생물 의학 마이크로 대 한 굴절 인덱스 일치 장치 제조

The use of microfluidic devices has emerged as a defining tool for biomedical applications. When combined with modern microscopy techniques, these devices ...

Double Emulsion Generation Using a Polydimethylsiloxane (PDMS) Co-axial Flow Focus Device

Double emulsions are useful in a number of biological and industrial applications in which it is important to have an aqueous carrier fluid. This paper presents a polydimethylsiloxane (PDMS) microfluidic device capable of generating water/oil/water double emulsions using a coaxial flow focusing geometry that can be fabricated entirely using soft lithography. Similar to emulsion devices using glass capillaries, double emulsions can be formed in channels with uniform wettability and with dimensions much smaller than the channel sizes. Three dimensional flow focusing geometry is achieved by casting a pair of PDMS slabs using two layer soft lithography, then mating the slabs together in a clamshell configuration. Complementary locking features molded into the PDMS slabs enable the accurate registration of features on each of the slab surfaces. Device testing demonstrates formation of double emulsions from 14 &#181;m to 50 &#181;m in diameter while using large channels that are robust against fouling and clogging.

Double Emulsion Generation Using a Polydimethylsiloxane PDMS Co-axial Flow Focus Device

Microfluidic double emulsions generation typically involves devices with patterned wettability or custom-fabricated glass components. Here we describe the fabrication and testing of an all polydimethylsiloxane (PDMS) double emulsion generator that does not require surface treatment or complicated fabrication processes, and is capable of producing double emulsions down to 14 &#181;m.

폴리 디메틸 실록산 (PDMS) 공동 축류 초점 장치를 사용하여 이중 에멀젼 생성

Double emulsions are useful in a number of biological and industrial applications in which it is important to have an aqueous carrier fluid. This paper ...

Window on a Microworld: Simple Microfluidic Systems for Studying Microbial Transport in Porous Media

Microbial growth and transport in porous media have important implications for the quality of groundwater and surface water, the recycling of nutrients in the environment, as well as directly for the transmission of pathogens to drinking water supplies. Natural porous media is composed of an intricate physical topology, varied surface chemistries, dynamic gradients of nutrients and electron acceptors, and a patchy distribution of microbes. These features vary substantially over a length scale of microns, making the results of macro-scale investigations of microbial transport difficult to interpret, and the validation of mechanistic models challenging. Here we demonstrate how simple microfluidic devices can be used to visualize microbial interactions with micro-structured habitats, to identify key processes influencing the observed phenomena, and to systematically validate predictive models. Simple, easy-to-use flow cells were constructed out of the transparent, biocompatible and oxygen-permeable material poly(dimethyl siloxane). Standard methods of photolithography were used to make micro-structured masters, and replica molding was used to cast micro-structured flow cells from the masters. The physical design of the flow cell chamber is adaptable to the experimental requirements: microchannels can vary from simple linear connections to complex topologies with feature sizes as small as 2 &mu;m. Our modular EcoChip flow cell array features dozens of identical chambers and flow control by a gravity-driven flow module. We demonstrate that through use of EcoChip devices, physical structures and pressure heads can be held constant or varied systematically while the influence of surface chemistry, fluid properties, or the characteristics of the microbial population is investigated. Through transport experiments using a non-pathogenic, green fluorescent protein-expressing Vibrio bacterial strain, we illustrate the importance of habitat structure, flow conditions, and inoculums size on fundamental transport phenomena, and with real-time particle-scale observations, demonstrate that microfluidics offer a compelling view of a hidden world.

Microfluidic devices can be used to visualize complex natural processes in real time and at the appropriate physical scales. We have developed a simple microfluidic device that mimics key features of natural porous media for studying growth and transport of bacteria in the subsurface.

다공성 매체에서 미생물 교통 유학에 대한 간단한 Microfluidic 시스템 : 미생물의 창

Microbial growth and transport in porous media have important implications for the quality of groundwater and surface water, the recycling of nutrients in ...

A Paired Bead and Magnet Array for Molding Microwells with Variable Concave Geometries

A spheroid culture is a useful tool for understanding cellular behavior in that it provides an in vivo-like three-dimensional environment. Various spheroid production methods such as non-adhesive surfaces, spinner flasks, hanging drops, and microwells have been used in studies of cell-to-cell interaction, immune-activation, drug screening, stem cell differentiation, and organoid generation. Among these methods, microwells with a three-dimensional concave geometry have gained the attention of scientists and engineers, given their advantages of uniform-sized spheroid generation and the ease with which the responses of individual spheroids can be monitored. Even though cost-effective methods such as the use of flexible membranes and ice lithography have been proposed, these techniques incur serious drawbacks such as difficulty in controlling the pattern sizes, achievement of high aspect ratios, and production of larger areas of microwells. To overcome these problems, we propose a robust method for fabricating concave microwells without the need for complex high-cost facilities. This method utilizes a 30 x 30 through-hole array, several hundred micrometer-order steel beads, and magnetic force to fabricate 900 microwells in a 3 cm x 3 cm polydimethylsiloxane (PDMS) substrate. To demonstrate the applicability of our method to cell biological applications, we cultured adipose stem cells for 3 days and successfully produced spheroids using our microwell platform. In addition, we performed a magnetostatic simulation to investigate the mechanism, whereby magnetic force was used to trap the steel beads in the through-holes. We believe that the proposed microwell fabrication method could be applied to many spheroid-based cellular studies such as drug screening, tissue regeneration, stem cell differentiation, and cancer metastasis.

This manuscript introduces a robust method of fabricating concave microwells without the need for complex high-cost facilities. Using magnetic force, steel beads, and a through-hole array, several hundred microwells were formed in a 3 cm x 3 cm polydimethylsiloxane (PDMS) substrate.