この作品は、Adeola Adewola、NIH / NCRR（U42RR023245）ホセオベールホルツァーへ、そしてシカゴの糖尿病のプロジェクトにAAUW国際フェローシップによってサポートされていました。

3層構造マイクロ流体perifusionデバイスのA.の微細加工底もマスタープロトコル（150μmの深井戸） <ol><li>必要に応じて、カミソリの刃を用いてウェハをクリーニングします。アセトン、メタノール、及びIPAで清掃してください。 30秒、50ワットでのプラズマ処理を実行</li><li>スピンSU8 - 100 @ 2000 rpmで。 [ステップ1：500回転、10秒、100回転/秒、ステップ2：2000回転、30秒、300rpmで/秒]。 [注：SU8を回転した後、ピンセットでウエハを保持していない] </li><li>ソフトベークで65ウェーハ℃で20分間、95℃で50分間C。 </li><li>ウェハは、所望のマスクを通してUV光にさらされています。 150μmの高さのための投与量は650ミリジュール/ cm 2である。 </li><li>露光後は65でウエハを焼く℃で1分間及び95℃Cで12分間。 </li><li> 15分間SU8開発者のウェーハを開発する。 </li></ol>マイクロチャネルマスターのプロトコル（500μmの深井戸） <ol><li>必要に応じて、カミソリの刃を用いてウェハをクリーニングします。アセトン、メタノール、及びIPAで清掃してください。 30秒、50ワットでのプラズマ処理を実行</li><li>スピンSU8 - 2150 @ 1000 rpmで。 [ステップ1：500回転、10秒、100回転/秒、ステップ2：1000回転、30秒、300rpmで/秒]。 </li><li>ソフトベーク65℃ウェハ° Cで1​​5分間、95℃で2時間と30分間。 </li><li>ウェハは、所望のマスクを通してUV光にさらされています。 650μmの高さのための露光量は685 MJ / cm 2である。 </li><li>露光後は65でウエハを焼く℃で5分間と95℃〜35分間。 </li><li> 20〜30分のためのSU8開発者のウェーハを開発する。 </li></ol> PDMSの溶液の調製<ol><li>ポリジメチルシロキサン（PDMS）ソリューションは、完全に標準Sylgard 184キットの硬化剤1部とシリコーンエラストマーの10部を混合することによって調製される。 </li><li>混合プロセス中にPDMSの溶液中で生成された気泡は、真空デシケーターを使用して削除されます。 </li><li>泡のないPDMSの溶液を徐々にSU8マスターと第三層のための空のペトリ皿上に分配される。 </li><li>ホットプレートの温度を75に設定されています° CとPDMSは2時間、この温度で​​硬化させる</li><li>インレット、アウトレットと交換ウェルを適当な大きさの穴パンチャーを使用して打ち抜かれている。 </li><li>層は、ハンドヘルドプラズマ装置を用いてスライドガラス（サイズ0.1 mm）に一緒に結合されています。 </li></ol> B.実験セットアップ<ol><li>マイクロデバイスを介してフローを70％エタノールで滅菌する。フローDIは、水、エタノールを洗い流すこと。マイクロチャネルの壁にインスリンの非特定の吸着を防止するためにデバイスを介して0.5％BSAを50mlを灌流。 </li><li>グルコースのランプの勾配とシリンジポンプは勾配が安定していることを確認するためにテストされていると通信するLabVIEWソフトウェアで生成された他の関連グラデーション。 </li><li> 25から30マウスの膵島は37℃で30分間、5μMのFura-2/AM（カルシウムインジケーター、分子プローブ、CA）および2.5μMのローダミン123（Rh123、ミトコンドリア電位のインジケータ、シグマ、MO）とともにインキュベートした2mMのグルコースを含むクレブス - リンガー緩衝液（KRB） </li><li>マウスの膵島は、慎重に入口ポートを通じて流体perifusionデバイスにピペッティングしている。 </li><li>マイクロ流体ネットワークは、タイゴンチューブとYコネクタやフラクションコレクターへのコンセントを使用してシリンジポンプへの入口を接続することにより、セットアップです。デバイスは、顕微鏡で加熱ステージ（37℃）上にあり、入口配管は、37室と溶液の温度を保つためにホットプレート上で加熱℃に</li><li>すぐにセットアップした後、マウスの膵島は、KRBは、その後、10分および25分のためのグルコースのランプ（2mMの25ミリメートル）に2 mMのグルコースを含むでperifusedされています。 </li><li>タイムラプス画像はSimplePCIソフトウェアによってすべての15秒を収集し、分析されています。 perifusateはまたELISAキットを用いてインスリン分泌を分析するためにフラクションコレクターを使用して分単位で収集される。 </li></ol>代表的な結果マウスの膵島は、2月25日mMグルコースの直線勾配でperifusedていた。図1に示すように、カルシウムの流入とインスリン分泌は、6 mMのグルコースに相当するperifusionの約13分、後にトリガされます。ミトコンドリア電位の変化は、約11分で、以前予想されると見られている。このデータは、膵島の生理学を特徴づけるためにこのマイクロ流体ネットワークを使用する利点を示しています。 <img src="/files/ftp_upload/1649/1649fig1.jpg" alt="図1" /> 図1。細胞の刺激を小島に生理反応。

<ol>
	<li>Mohammed, J. S., Wang, Y., Harvat, T. A., Oberholzer, J., Eddington, D. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Microfluidic+device+for+multimodal+characterization+of+pancreatic+islets.">Microfluidic device for multimodal characterization of pancreatic islets.</a> Lab Chip. 9, 97-106 (2009).</li></ol>

伝統的な膵島perifusionシステムは、（マクロスケールとマイクロスケール）設定とデザイン、高い技術要件、およびシステム内のユーザ所定の化学的勾配を作成するには難しさの複雑なを含むいくつかの制限があります。ここで説明するマイクロ流体perifusionシステムは、設計と製造のシンプルな形状で、これらの制限を克服しています。さらに重要なことは、このシステムは、膵島生理学を?...

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		<th>Material Name</th>
		<th>Type</th>
		<th>Company</th>
		<th>Catalogue Number</th>
		<th>Comment</th>
		</tr>
		</thead>
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<tr>
<td>60ml Syringes</td>
<td>&nbsp;</td>
<td>BD</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Fura-2 fluorescence dye</td>
<td>&nbsp;</td>
<td>Molecular Probes Inc.</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Rhodamine123 Fluorescence dye</td>
<td>&nbsp;</td>
<td>Molecular Probes Inc.</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Glucose</td>
<td>&nbsp;</td>
<td>Sigma</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Bovine Serum Albumin</td>
<td>&nbsp;</td>
<td>Sigma</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>30" Silicone tubings</td>
<td>&nbsp;</td>
<td>Cole Palmer</td>
<td>&nbsp;</td>
<td>1/16 x 1/8in</td>
</tr>
<tr>
<td>1.5ml Eppendorf tubes</td>
<td>&nbsp;</td>
<td>Fisher</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Y-connectors</td>
<td>&nbsp;</td>
<td>Cole Palmer</td>
<td>&nbsp;</td>
<td>1/16&#x201D; &amp; 4mm</td>
</tr>
<tr>
<td>Syringe connectors</td>
<td>&nbsp;</td>
<td>Cole Palmer</td>
<td>&nbsp;</td>
<td>female luer plug 1/16&#x201D;</td>
</tr>
<tr>
<td>Straight connectors</td>
<td>&nbsp;</td>
<td>Cole Palmer</td>
<td>&nbsp;</td>
<td>1/16&#x201D;</td>
</tr>
<tr>
<td>Elbow connector</td>
<td>&nbsp;</td>
<td>Cole Palmer</td>
<td>&nbsp;</td>
<td>1/16&#x201D;</td>
</tr>
<tr>
<td>Havard syringe pump</td>
<td>&nbsp;</td>
<td>Harvard Apparatus</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Perifusion device</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Hot plate</td>
<td>&nbsp;</td>
<td>PMC</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Thermometer</td>
<td>&nbsp;</td>
<td>Omega Engineering Inc.</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Fraction collector</td>
<td>&nbsp;</td>
<td>Gibson</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Pippettor</td>
<td>&nbsp;</td>
<td>Fisher</td>
<td>&nbsp;</td>
<td>&nbsp;</td>
<tr>
<td>Inverted epiflorescence microscope</td>
<td>&nbsp;</td>
<td>Olympus</td>
<td>IX71</td>
<td>&nbsp;</td>
<tr>
<td>Charge-coupled device</td>
<td>&nbsp;</td>
<td>QImaging</td>
<td>&nbsp;</td>
<td>Retiga-SRV, Fast 1394</td>
</tr>		</tbody>
		</table>
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a multi-parametric islet perifusion system within a microfluidic perifusion device

マイクロ流体膵島perifusionデバイスは、複数の島とカルシウム流入とミトコンドリアの潜在的な変化の同時蛍光イメージングの動的なインスリン分泌の評価のために開発されました。装置は3つの層から構成されています：最初の層は、島の露出表面積を流れると、最大化するために露出しながら島を固定するために役立つマイクロウェル（500μmの直径は150μmの深さ）の配列を含み、第二層は円形が含まれていますperifusion室（深さ3 mmの7mmの直径）、および第3層は入口ミキシングチャンネルが含まれており、ファンアウトの前に最適化するためのperifusionチャンバ内へ注入（幅2 mm、長さ19ミリ、高さは500μm）混合効率は、前perifusion室に入る。リニア、ベルの形状を含む様々なグルコースの勾配、および正方形の形状の作成もマイクロ流体perifusionのネットワーク内に作成することができると示されている。

Watch this Scientific Journal Video about A Multi-Parametric Islet Perifusion System within a Microfluidic Perifusion Device at JoVE.com

A Multi-Parametric Islet Perifusion System within a Microfluidic Perifusion Device

マイクロ流体膵島perifusionデバイスは、複数の島とカルシウム流入とミトコンドリアの潜在的な変化の同時蛍光イメージングの動的なインスリン分泌の評価のために開発されました。

マイクロ流体Perifusionデバイス内のマルチパラメトリック膵島Perifusionシステム

A microfluidic islet perifusion device was developed for the assessment of dynamic insulin secretion of multiple islets and simultaneous fluorescence ...

a-multi-parametric-islet-perifusion-system-within-microfluidic

Research

JoVE Journal

Biology

11.8K ビュー.  University of Illinois, Chicago. マイクロ流体膵島perifusionデバイスは、複数の島とカルシウム流入とミトコンドリアの潜在的な変化の同時蛍光イメージングの動的なインスリン分泌の評価のために開発されました。

ビデオ: A Multi-Parametric Islet Perifusion System within a Microfluidic Perifusion Device

Murine Pancreatic Islet Isolation

マウス膵島単離

生物学

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.

ニューロン相馬と軸索のコンパートメントのためのマイクロ流体デバイスの作製

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

A Microfluidic Device with Groove Patterns for Studying Cellular Behavior

We describe a microfluidic device with microgrooved patterns for studying cellular behavior. This microfluidic platform consists of a top fluidic channel and a bottom microgrooved substrate. To fabricate the microgrooved channels, a top poly(dimethylsiloxane) (PDMS) mold containing the impression of the microfluidic channels was aligned and bonded to a microgrooved substrate. Using this device, mouse fibroblast cells were immobilized and patterned within microgrooved substrates (25, 50, 75, and 100 &mu;m wide). To study apoptosis in a microfluidic device, media containing hydrogen peroxide, Annexin V, and propidium iodide was perfused into the fluidic channel for 2 hours. We found that cells exposed to the oxidative stress became apoptotic. These apoptotic cells were confirmed by Annexin V that bound to phosphatidylserine at the outer leaflet of the plasma membrane during the apoptosis process. Using this microfluidic device with microgrooved patterns, the apoptosis process was observed in real-time and analyzed by using an inverted microscope containing an incubation chamber (37&deg;C, 5% CO2). Therefore, this microfluidic device incorporated with microgrooved substrates could be useful for studying the cellular behavior and performing high-throughput drug screening.

We describe a protocol for the fabrication of microfluidic devices that can enable cell capture and culture. In this approach patterned microstructures such as grooves within microfluidic channels are used to create low shear stress regions within which cell can dock.

細胞挙動を研究するための溝パターンを用いたマイクロ流体デバイス

We describe a microfluidic device with microgrooved patterns for studying cellular behavior.  This microfluidic platform consists of a top fluidic channel ...

A Gradient-generating Microfluidic Device for Cell Biology

 The fabrication and operation of a gradient-generating microfluidic device for studying cellular behavior is described.  A microfluidic platform is an enabling experimental tool, because it can precisely manipulate fluid flows, enable high-throughput experiments, and generate stable soluble concentration gradients.  Compared to conventional gradient generators, poly(dimethylsiloxane) (PDMS)-based  microfluidic devices can generate stable concentration gradients of growth factors with well-defined profiles.  Here, we developed simple gradient-generating microfluidic devices with three separate inlets.  Three microchannels combined into one microchannel to generate concentration gradients.  The stability and shape of growth factor gradients were confirmed by fluorescein isothyiocyanate (FITC)-dextran with a molecular weight similar to epidermal growth factor (EGF).  Using this microfluidic device, we demonstrated that fibroblasts exposed to concentration gradients of EGF migrated toward higher concentrations.  The directional orientation of cell migration and motility of migrating cells were quantitatively assessed by cell tracking analysis.  Thus, this gradient-generating microfluidic device might be useful for studying and analyzing the behavior of migrating cells.

We describe a protocol for the microfabrication of the gradient-generating microfluidic device that can generate spatial and temporal gradients in well-defined microenvironment. In this approach, the gradient-generating microfluidic device can be used to study directed cell migration, embryogenesis, wound healing, and cancer metastasis.

細胞生物学の勾配を生むマイクロ流体デバイス

 The fabrication and operation of a gradient-generating microfluidic device for studying cellular behavior is described.  A microfluidic platform is an ...

Preparing E18 Cortical Rat Neurons for Compartmentalization in a Microfluidic Device

In this video, we demonstrate the preparation of E18 cortical rat neurons. E18 cortical rat neurons are obtained from E18 fetal rat cortex previously dissected and prepared. The E18 cortex is, upon dissection, immediately dissociated into individual neurons. It is possible to store E18 cortex in Hibernate E buffer containing B27 at 4&deg;C for up to a week before the dissociation is performed. However, there will be a drop in cell viability. Typically we obtain our E18 Cortex fresh. It is transported to the lab in ice cold Calcium free Magnesium free dissection buffer (CMFM). Upon arrival, trypsin is added to the cortex to a final concentration of 0.125%. The cortex is then incubated at 37&deg;C for 8 minutes. DMEM containing 10% FBS is added to the cortex to stop the reaction. The cortex is then centrifuged at 2500 rpm for 2 minutes. The supernatant is removed and 2 ml of Neural Basal Media (NBM) containing 2% B27 (vol/vol) and 0.25% Glutamax (vol/vol) is added to the cortex which is then re-suspended by pipetting up and down. Next, the cortex is triturated with previously fire polished glass pipettes, each with a successive smaller opening. After triturating, the cortex is once again centrifuged at 2500 rpm for 2 minutes. The supernatant is then removed and the cortex pellet re-suspended with 2 ml of NBM containing B27 and Glutamax. The cell suspension is then passed through a 40 um nylon cell strainer. Next the cells are counted. The neurons are now ready for loading into the neuron microfluidic device.

In this video we demonstrate the preparation of E18 Cortical Rat Neurons.

マイクロ流体デバイスでコンパートメントのためのE18脳ラットのニューロンの準備

In this video, we demonstrate the preparation of E18 cortical rat neurons. E18 cortical rat neurons are obtained from E18 fetal rat cortex previously ...

Cell Capture Using a Microfluidic Device

マイクロ流体デバイスを用いた細胞のキャプチャ

Assessing Neural Stem Cell Motility Using an Agarose Gel-based Microfluidic Device

While microfluidic technology is reaching a new level of maturity for macromolecular assays, cell-based assays are still at an infant stage1. This is largely due to the difficulty with which one can create a cell-compatible and steady microenvironment using conventional microfabrication techniques and materials. We address this problem via the introduction of a novel microfabrication material, agarose gel, as the base material for the microfluidic device. Agarose gel is highly malleable, and permeable to gas and nutrients necessary for cell survival, and thus an ideal material for cell-based assays. We have shown previously that agarose gel based devices have been successful in studying bacterial and neutrophil cell migration2. In this report, three parallel microfluidic channels are patterned in an agarose gel membrane of about 1mm thickness. Constant flows with media/buffer are maintained in the two side channels using a peristaltic pump. Cells are maintained in the center channel for observation. Since the nutrients and chemicals in the side channels are constantly diffusing from the side to center channel, the chemical environment of the center channel is easily controlled via the flow along the side channels. Using this device, we demonstrate that the movement of neural stem cells can be monitored optically with ease under various chemical conditions, and the experimental results show that the over expression of epidermal growth factor receptors (EGFR) enhances the motility of neural stem cells. Motility of neural stem cells is an important biomarker for assessing cells aggressiveness, thus tumorigenic factor3. Deciphering the mechanism underlying NSC motility will yield insight into both disorders of neural development and into brain cancer stem cell invasion.

We demonstrate that the over expression of epidermal growth factor receptors (EGFR) enhances the motility of neural stem cells(NSCs) using a novel agarose gel based microfluidic device. This technology can be readily adaptable to other mammalian cell systems where cell sources are scarce, such as human neural stem cells, and the turn around time is critical.

アガロースゲルベースの​​マイクロ流体デバイスを用いた神経幹細胞運動の評価

While microfluidic technology is reaching a new level of maturity for macromolecular assays, cell-based assays are still at an infant stage1. This is ...

A Multi-compartment CNS Neuron-glia Co-culture Microfluidic Platform

We present a novel multi-compartment neuron co-culture microsystem platform for in vitro CNS axon-glia interaction research, capable of conducting up to six independent experiments in parallel for higher-throughput. We developed a new fabrication method to create microfluidic devices having both micro and macro scale structures within the same device through a single soft-lithography process, enabling mass fabrication with good repeatability.
The multi-compartment microfluidic co-culture platform is composed of one soma compartment for neurons and six axon/glia compartments for oligodendrocytes (OLs). The soma compartment and axon/glia compartments are connected by arrays of axon-guiding microchannels that function as physical barriers to confine neuronal soma in the soma compartment, while allowing axons to grow into axon/glia compartments. OLs loaded into axon/glia compartments can interact only with axons but not with neuronal soma or dendrites, enabling localized axon-glia interaction studies. The microchannels also enabled fluidic isolation between compartments, allowing six independent experiments to be conducted on a single device for higher throughput.
Soft-lithography using poly(dimethylsiloxane) (PDMS) is a commonly used technique in biomedical microdevices. Reservoirs on these devices are commonly defined by manual punching. Although simple, poor alignment and time consuming nature of the process makes this process not suitable when large numbers of reservoirs have to be repeatedly created. The newly developed method did not require manual punching of reservoirs, overcoming such limitations. First, seven reservoirs (depth: 3.5 mm) were made on a poly(methyl methacrylate) (PMMA) block using a micro-milling machine. Then, arrays of ridge microstructures, fabricated on a glass substrate, were hot-embossed against the PMMA block to define microchannels that connect the soma and axon/glia compartments. This process resulted in macro-scale reservoirs (3.5 mm) and micro-scale channels (2.5 &mu;m) to coincide within a single PMMA master. A PDMS replica that served as a mold master was obtained using soft-lithography and the final PDMS device was replicated from this master.
Primary neurons from E16-18 rats were loaded to the soma compartment and cultured for two weeks. After one week of cell culture, axons crossed microchannels and formed axonal only network layer inside axon/glia compartments. Axons grew uniformly throughout six axon/glia compartments and OLs from P1-2 rats were added to axon/glia compartments at 14 days in vitro for co-culture.

We developed a novel multi-compartment neuron co-culture microsystem platform for in vitro CNS axon-glia interaction research. The platform is capable of conducting up to six independent experiments in parallel and was fabricated using a newly developed macro/micro hybrid fabrication method.

マルチコンパートメントのCNSニューロングリア共培養マイクロ流体プラットフォーム

We present a novel multi-compartment neuron co-culture microsystem platform for in vitro CNS axon-glia interaction research, capable of conducting up to ...

The Microfluidic Probe: Operation and Use for Localized Surface Processing

Microfluidic devices allow assays to be performed using minute amounts of sample and have recently been used to control the microenvironment of cells. Microfluidics is commonly associated with closed microchannels which limit their use to samples that can be introduced, and cultured in the case of cells, within a confined volume. On the other hand, micropipetting system have been used to locally perfuse cells and surfaces, notably using push-pull setups where one pipette acts as source and the other one as sink, but the confinement of the flow is difficult in three dimensions. Furthermore, pipettes are fragile and difficult to position and hence are used in static configuration only. 
The microfluidic probe (MFP) circumvents the constraints imposed by the construction of closed microfluidic channels and instead of enclosing the sample into the microfluidic system, the microfluidic flow can be directly delivered onto the sample, and scanned across the sample, using the MFP. . The injection and aspiration openings are located within a few tens of micrometers of one another so that a microjet injected into the gap is confined by the hydrodynamic forces of the surrounding liquid and entirely aspirated back into the other opening. The microjet can be flushed across the substrate surface and provides a precise tool for localized deposition/delivery of reagents which can be used over large areas by scanning the probe across the surface. 
In this video we present the microfluidic probe1 (MFP). We explain in detail how to assemble the MFP, mount it atop an inverted microscope, and align it relative to the substrate surface, and finally show how to use it to process a substrate surface immersed in a buffer.

In this video we present the microfluidic probe1 (MFP). We explain in detail how to assemble the MFP, mount it atop an inverted microscope, and align it relative to the substrate surface, and finally show how to use it to process a substrate surface immersed in a buffer solution.

マイクロ流体プローブ：局在表面処理のための操作と使用方法

Microfluidic devices allow assays to be performed using minute amounts of sample and have recently been used to control the microenvironment of cells. ...

Platelet Adhesion and Aggregation Under Flow using Microfluidic Flow Cells

Platelet aggregation occurs in response to vascular injury where the extracellular matrix below the endothelium has been exposed. The platelet adhesion cascade takes place in the presence of shear flow, a factor not accounted for in conventional (static) well-plate assays. This article reports on a platelet-aggregation assay utilizing a microfluidic well-plate format to emulate physiological shear flow conditions. Extracellular proteins, collagen I or von Willebrand factor are deposited within the microfluidic channel using active perfusion with a pneumatic pump. The matrix proteins are then washed with buffer and blocked to prepare the microfluidic channel for platelet interactions. Whole blood labeled with fluorescent dye is perfused through the channel at various flow rates in order to achieve platelet activation and aggregation. Inhibitors of platelet aggregation can be added prior to the flow cell experiment to generate IC50 dose response data.

The platelet adhesion cascade takes place in the presence of shear flow, a factor not accounted for in conventional (static) well-plate assays. This article reports on a platelet-aggregation assay utilizing a microfluidic well-plate format to emulate physiological shear flow conditions.

マイクロ流体フローセルを使用して流れの下で血小板粘着と凝集

Platelet aggregation occurs in response to vascular injury where the extracellular matrix below the endothelium has been exposed. The platelet adhesion ...