The authors would like to acknowledge the BPI PIAVE AUTONOTEX grant for the financial support.

1.パターニングは、繊維上の導電性高分子<ol><li>処理中に簡単に処理するための平坦な表面上の10センチメートル×10センチの繊維シートを修正しました。織物の場合は、300ミクロンの厚さと、50％までのニット方向ストレッチ機能を持つ100％インターロックニットポリエステル生地を使用。 </li><li>パターニング設計を含むマスクを作成するには、125μmの厚さのポリイミドフィルムを使用します。パターンの例が図1に示されています。 <ol><li>パターンにポリイミドマスク10をレーザーカッター（ 例えば、Protolaser S、LPKF）を使用します。電極のパターン設計は、 図1に示されています。 </li><li>コートPDMS物（10：1塩基剤比を硬化する）は200μmとでの湿潤膜厚で自動テープキャスティングツール（K制御プリントコーター、ドクターブレード）を用いて、マスク（ポリイミドフィルム）の上6m /秒分の塗布速度。 3センチメートルのx 5cmのマスクのために約0.5ミリリットルを使用してください。目を実行しますヒュームフードの下でプロセスです。 </li></ol></li><li>静かにPDMSでコーティングされたマスクに生地を移します。 PDMSは、完全に織物構造に吸収されるべき後、10分間のままにしておきます。 </li><li> 10分間、100℃の空気オーブン中でサンプルを硬化します。 </li><li>導電性ポリマーを準備：PEDOT：PSS分散液（80ミリリットル）、エチレングリコール（20mL）で、4 - ドデシルベンゼンスルホン酸（40μL）、およびヒュームフード中の3-メタクリロ（1ミリリットル）。 </li><li>ブラシコートPEDOT：溶液の均一な浸透まで織物のPDMSを含まない領域にPSS溶液が得られます。均一なパターンの色を達成するために、この手順を繰り返します。約1mL / cm 2で適用します。 </li><li> PSS溶液：PEDOTを乾燥させるために1時間、110℃で生地を治します。ナイロンのような高温処理に敏感である織物、60℃に温度を下げてください。 </li></ol> 2.有機デバイスの製造注：第1 describでプロトコル織物上の導電材料の選択的堆積をエス。次のセクションでは、ストレッチセンサ、OECTトランジスタ、皮膚電極、および容量センサのように、有機デバイスを製造するために必要な追加手順について説明します。 <ol><li>セクション1で説明したように、織物の図3aに示されるストレッチセンサ、パターン電極線を製造するために、1.1〜1.5ステップ。 注：パターン設計の例は、 図3aに示されています。このようなセンサの製造は、任意の追加の手順は必要ありません。 </li><li> 図3bに示すトランジスタの設計を製造するために、パターン1節で説明する手順以下のナイロン織リボン上のトランジスタアレイは、わずかにPDMSのアニーリングおよびPEDOTを変更：PSSは、60℃で硬化させることによりナイロンの熱劣化を回避するために手順を硬化させます長い時間のためのC。 </li><li> 図3cに示される皮膚電極の製造については、堆積パターン化されたPEDOT上のイオン性ゲル：PSSテキスタイル。 <ol><li>イオン液体、1-エチル-3-メチルイミダゾリウム・エチル硫酸塩を含むイオン性液体ゲル混合物を調製します。架橋剤としては、ポリ（エチレングリコール）ジアクリレート。それぞれ、0.6 / 0.35 / 0.05の（v / v）の比で光開始剤、2-ヒドロキシ-2-メチルプロピオフェノン。 </li><li>コートPEDOT：イオン液体（20μL/ cm 2）を持つPSS電極とドロップキャスティングによって（25μL/ cm 2）をステップ2.3.1からイオン性液体ゲル混合物を追加します。 </li><li>ゲルが固化するまで、10〜15分間架橋反応を開始するためにUV光（365 nm）に露光します。ドラフト内で、この手順を実行します。 UV露光中にUV-保護ケージを使用してください。 </li></ol></li><li>静電容量センサの製造のために、PEDOTを使用：PSSのテキスタイル電極は、絶縁材料（ 図3d）で絶縁。 <ol><li>キーボードのようなPEDOT絶縁：PDMSを使用して、PSS電極を、キーボードのデザインは、&lt;図2bに見られます/ strong&gt;の。生地の上にPDMS製剤を分配し、スキージで過剰を取り除きます。 </li><li> 10分間100℃のオーブンで生地を置きます。ドラフト内で、この手順を実行します。 </li></ol></li></ol>

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The authors have nothing to disclose.

導電性材料のパターニングは、機能的な電子デバイスの製造における最初のステップの1つです。製造プロセスは、アカウントにこのような材料の化学的および物理的特性を取る必要があり、プロセスフローは、製造工程の間に材料の相互互換性を考慮する必要があるので、これは、挑戦的になることができます。有機電子デバイスの微細加工では、これらの2つの側面が原因有機物の高度に?...

ウェアラブルエレクトロニクスの分野では3回、現在の市場の上、2025年に500億ユーロの価値があると予想される急成長している市場です。現在のウェアラブルデバイスが直面する主な課題は、侵入型固体電子添付ファイルがウェアラブルシステムで確立されたデバイスの使用を制限しているということです。日常生活の中ですでに存在している繊維製品を使用することでこの制限を回避するために非常に魅力的かつ直接的なアプローチです。 、その弾性能力を、私たちが着る衣服の一部が皮膚に密着して自然にあります。市場で入手可能なスマート服の多くの例は、今日はファッショナブルな方法1で人間と電子機器をつなぐ、薄い、プラスチックディスプレイ、キーボード、および織物に埋め込まれた光源装置に基づいています。スポーツの練習では、ヘルスモニタリングは、一般的に、接着剤、電極と金属リストバンドを使用するために快適な選択肢を提供するテキスタイル電極、に依存しています。ここでは、導電性繊維であります直接長時間着用中に皮膚刺激やその他の不快感を防ぐために、伸縮性のある生地と統合。また、テキスタイルは、運動2をキャプチャするために、曲率センサを統合する機能ロボットアクチュエータ3の開発のためのせん断センサーを統合するために、そして確かに汗4中の検体を検出することによりバイオセンサーを統合するために多くの機会を提供しています。 現代の着用可能な技術は、独自の特性を有する電子デバイスを提供炭素系半導体材料に依存します。有機物の「ソフト」な性質は、従来の固体エレクトロニクスに比べ、人体とのインタフェースのための良好な機械的性質を提供しています。機械的にフレキシブル基板とペアこの機械的適合性は、そのような繊維のような装置における非平面形状因子の使用を可能にします。有機物の使用は、これらの混合ELEに生命科学にも関連していますctronicとイオン伝導性5。また、有機半導体および光電子材料は、ディスプレイ、トランジスタ、ロジック、および電源機能6、7、8、9を有する機能素子の多種多様な力を与えます。このような有機デバイスの製造における主な困難は、繊維の非平面表面上の機能材料の制御された沈着です。従来の微細加工技術は、主に織物基材の構造的次元を有する堆積プロセスの不適合性によって制限されます。 ここでは、構造化繊維製品上の導電性ポリマーの選択的な堆積を可能にし、シンプルでスケーラブルな製造プロトコルを記述します。提示方法は、ウェアラブルとコンフォーマル電子デバイスの製造を可能にします。アプローチは、Cのパターンに基づいていますommercially利用可能な導電性ポリマー、ポリ（3,4-エチレンジオキシチオフェン）：ポリ（スチレンスルホネート）（PEDOT：PSS）及び織物のエラストマーステンシル材料、ポリジメチルシロキサン（PDMS）。この組み合わせは、水性PEDOTの効率的な閉じ込めを可能にする：PSS溶液、ならびに繊維製品のソフトで伸縮性の特性を保持するため。このシンプルで信頼性の高い製造方法は、費用効率的かつ工業的にスケーラブルな方法で直接繊維製品上のさまざまな電子機器を製造するための道を開きます。

<table border="0" cellpadding="0" cellspacing="0" width="748">
	<colgroup>
		<col />
		<col />
		<col />
		<col />
	</colgroup>
	<tbody>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">SYLGARD 184, Silicone elastomer kit (Base and Curing agent)</td>
			<td style="width:159px;">Dow Corning</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">PDMS elastomer</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="21">
			<td colspan="4" height="21" style="height:21px;width:748px;">The conducting polymer formulation</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;">CleviosTM PH 1000 PEDOT:PSS</td>
			<td style="width:159px;">Heraeus</td>
			<td style="width:119px;"></td>
			<td>Conductive polymer</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">Ethylene glycol</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">03750-250ML</td>
			<td>Solvent (EG), CAS: 107-21-1</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">3-methacryloxypropyltrimethoxysilane</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td>M6514</td>
			<td>Cros linker (GOPs), CAS: 2530-85-0</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">4-dodecylbenzenesulfonic acid</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">44198</td>
			<td>(DBSA), CAS: 121-65-3</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="21">
			<td colspan="4" height="21" style="height:21px;width:748px;">The ionic liquid gel</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">UV lamp DFE 2340</td>
			<td style="width:159px;">C.I.F/ ATHELEC</td>
			<td style="width:119px;">DP134</td>
			<td>UV-365nm</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">1-Ethyl-3-methylimidazolium ethyl sulfate</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">51682-100G-F</td>
			<td>Ionic Liquid (IL), CAS: 342573-75-5</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">Poly(ethylene glycol) diacrylate</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">455008-100ML</td>
			<td>Mn 700, CAS: 26570-48-9</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">2-Hydroxy-2-methylpropiophenon</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">405655-50ML</td>
			<td>Phot Initiator (PI), CAS: 7473-98-5</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">The textile fabric</td>
			<td style="width:159px;">VWR</td>
			<td style="width:119px;">Spec-Wipe 7 Wipers</td>
			<td>100% interlock knit polyester fabric</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;">The polyimide film</td>
			<td style="width:159px;">DuPont</td>
			<td style="width:119px;">HN100</td>
			<td>Polyimide film with 125 &#181;m thickness</td>
		</tr>
	</tbody>
</table>

a simple and scalable fabrication method for organic electronic devices on textiles

Today, wearable electronics devices combine a large variety of functional, stretchable, and flexible technologies. However, in many cases, these devices cannot be worn under everyday conditions. Therefore, textiles are commonly considered the best substrate to accommodate electronic devices in wearable use. In this paper, we describe how to selectively pattern organic electroactive materials on textiles from a solution in an easy and scalable manner. This versatile deposition technique enables the fabrication of wearable organic electronic devices on clothes.

織物に色やパターンを適用する従来の方法は、染料の選択的堆積を可能にするために取り外し可能なマスキング層に依存しています。織物上のPSS電極： 図1では、我々は、PEDOTのパターニングにこのようなアプローチの適応を示しています。 PSS溶液：マスキング層として、我々は、水性PEDOTの非制御可能な拡散を抑制することができる疎水性のポリジメチ?...

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A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles

本稿では、ウェアラブルと有機電子デバイスの直接統合を可能にする選択的織物上に有機材料を堆積するためのプロトコルを提示します。製造されたデバイスは、完全に機械的な外観を尊重し、検知機能を有効にする、繊維に組み込むことができます。

テキスタイル上の有機電子デバイスのためのシンプルでスケーラブルな製造方法

Today, wearable electronics devices combine a large variety of functional, stretchable, and flexible technologies. However, in many cases, these devices ...

a-simple-scalable-fabrication-method-for-organic-electronic-devices

Research

JoVE Journal

Bioengineering

10.3K ビュー.  Ecole Nationale Supérieure des Mines de Saint-Étienne, CMP-EMSE, MOC. 本稿では、ウェアラブルと有機電子デバイスの直接統合を可能にする選択的織物上に有機材料を堆積するためのプロトコルを提示します。製造されたデバイスは、完全に機械的な外観を尊重し、検知機能を有効にする、繊維に組み込むことができます。 

ビデオ: A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles

Simple Microfluidic Devices for in vivo Imaging of C. elegans, Drosophila and Zebrafish

Micro fabricated fluidic devices provide an accessible micro-environment for in vivo studies on small organisms. Simple fabrication processes are available for microfluidic devices using soft lithography techniques 1-3. Microfluidic devices have been used for sub-cellular imaging 4,5, in vivo laser microsurgery 2,6 and cellular imaging 4,7. In vivo imaging requires immobilization of organisms. This has been achieved using suction 5,8, tapered channels 6,7,9, deformable membranes 2-4,10, suction with additional cooling 5, anesthetic gas 11, temperature sensitive gels 12, cyanoacrylate glue 13 and anesthetics such as levamisole 14,15. Commonly used anesthetics influence synaptic transmission 16,17 and are known to have detrimental effects on sub-cellular neuronal transport 4. In this study we demonstrate a membrane based poly-dimethyl-siloxane (PDMS) device that allows anesthetic free immobilization of intact genetic model organisms such as Caenorhabditis elegans (C. elegans), Drosophila larvae and zebrafish larvae. These model organisms are suitable for in vivo studies in microfluidic devices because of their small diameters and optically transparent or translucent bodies. Body diameters range from ~10 &mu;m to ~800 &mu;m for early larval stages of C. elegans and zebrafish larvae and require microfluidic devices of different sizes to achieve complete immobilization for high resolution time-lapse imaging. These organisms are immobilized using pressure applied by compressed nitrogen gas through a liquid column and imaged using an inverted microscope. Animals released from the trap return to normal locomotion within 10 min.
We demonstrate four applications of time-lapse imaging in C. elegans namely, imaging mitochondrial transport in neurons, pre-synaptic vesicle transport in a transport-defective mutant, glutamate receptor transport and Q neuroblast cell division. Data obtained from such movies show that microfluidic immobilization is a useful and accurate means of acquiring in vivo data of cellular and sub-cellular events when compared to anesthetized animals (Figure 1J and 3C-F 4).
Device dimensions were altered to allow time-lapse imaging of different stages of C. elegans, first instar Drosophila larvae and zebrafish larvae. Transport of vesicles marked with synaptotagmin tagged with GFP (syt.eGFP) in sensory neurons shows directed motion of synaptic vesicle markers expressed in cholinergic sensory neurons in intact first instar Drosophila larvae. A similar device has been used to carry out time-lapse imaging of heartbeat in ~30 hr post fertilization (hpf) zebrafish larvae. These data show that the simple devices we have developed can be applied to a variety of model systems to study several cell biological and developmental phenomena in vivo.

Simple Microfluidic Devices for in vivo Imaging of C. elegans, Drosophila and Zebrafish

A simple microfluidic device has been developed to perform anesthetic free in vivo imaging of C. elegans, intact Drosophila larvae and zebrafish larvae. The device utilizes a deformable PDMS membrane to immobilize these model organisms in order to perform time lapse imaging of numerous processes such as heart beat, cell division and sub-cellular neuronal transport. We demonstrate the use of this device and show examples of different types of data collected from different model systems.

のためのシンプルなマイクロ流体デバイス<em生体内で&gt;</emの&gt;イメージング<em&gt; Cエレガンス</em&gt;<em&gt;ショウジョウバエ</em&gt;とゼブラフィッシュ

Micro fabricated fluidic devices provide an accessible micro-environment for in vivo studies on small organisms. Simple fabrication processes are ...

生物工学

Microfluidic Chip Fabrication and Method to Detect Influenza

Fast and effective diagnostics play an important role in controlling infectious disease by enabling effective patient management and treatment. Here, we present an integrated microfluidic thermoplastic chip with the ability to amplify influenza A virus in patient nasopharyngeal (NP) swabs and aspirates. Upon loading the patient sample, the microfluidic device sequentially carries out on-chip cell lysis, RNA purification and concentration steps within the solid phase extraction (SPE), reverse transcription (RT) and polymerase chain reaction (PCR) in RT-PCR chambers, respectively. End-point detection is performed using an off-chip Bioanalyzer (Agilent Technologies, Santa Clara, CA). For peripherals, we used a single syringe pump to drive reagent and samples, while two thin film heaters were used as the heat sources for the RT and PCR chambers. The chip is designed to be single layer and suitable for high throughput manufacturing to reduce the fabrication time and cost. The microfluidic chip provides a platform to analyze a wide variety of virus and bacteria, limited only by changes in reagent design needed to detect new pathogens of interest.

An integrated microfluidic thermoplastic chip has been developed for use as a molecular diagnostic. The chip performs nucleic acid extraction, reverse transcriptase, and PCR. Methods for fabricating and running the chip are described.

マイクロ流体チップの作製とインフルエンザを検出する方法

Fast  and effective diagnostics play an important role in controlling infectious  disease by enabling effective patient management and treatment. Here, we ...

Fabrication of a Functionalized Magnetic Bacterial Nanocellulose with Iron Oxide Nanoparticles

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

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

酸化鉄ナノ粒子との機能を有する磁性細菌Nanocelluloseの作製

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

Fabrication and Characterization of a Conformal Skin-like Electronic System for Quantitative, Cutaneous Wound Management

Recent advances in the development of electronic technologies and biomedical devices offer opportunities for non-invasive, quantitative assessment of cutaneous wound healing on the skin. Existing methods, however, still rely on visual inspections through various microscopic tools and devices that normally include high-cost, sophisticated systems and require well trained personnel for operation and data analysis. Here, we describe methods and protocols to fabricate a conformal, skin-like electronics system that enables conformal lamination to the skin surface near the wound tissues, which provides recording of high fidelity electrical signals such as skin temperature and thermal conductivity. The methods of device fabrication provide details of step-by-step preparation of the microelectronic system that is completely enclosed with elastomeric silicone materials to offer electrical isolation. The experimental study presents multifunctional, biocompatible, waterproof, reusable, and flexible/stretchable characteristics of the device for clinical applications. Protocols of clinical testing provide an overview and sequential process of cleaning, testing setup, system operation, and data acquisition with the skin-like electronics, gently mounted on hypersensitive, cutaneous wound and contralateral tissues on patients.

This article presents methods to fabricate and characterize a conformal, skin-like electronic system and protocols for the use in clinical applications, particularly on cutaneous wound management.

定量的、皮膚が創傷管理のためのコンフォーマルスキンのような電子システムの作製と評価

Recent advances in the development of electronic technologies and biomedical devices offer opportunities for non-invasive, quantitative assessment of ...

Biomembrane Fabrication by the Solvent-assisted Lipid Bilayer (SALB) Method

In order to mimic cell membranes, the supported lipid bilayer (SLB) is an attractive platform which enables in vitro investigation of membrane-related processes while conferring biocompatibility and biofunctionality to solid substrates. The spontaneous adsorption and rupture of phospholipid vesicles is the most commonly used method to form SLBs. However, under physiological conditions, vesicle fusion (VF) is limited to only a subset of lipid compositions and solid supports. Here, we describe a one-step general procedure called the solvent-assisted lipid bilayer (SALB) formation method in order to form SLBs which does not require vesicles. The SALB method involves the deposition of lipid molecules onto a solid surface in the presence of water-miscible organic solvents (e.g., isopropanol) and subsequent solvent-exchange with aqueous buffer solution in order to trigger SLB formation. The continuous solvent exchange step enables application of the method in a flow-through configuration suitable for monitoring bilayer formation and subsequent alterations using a wide range of surface-sensitive biosensors. The SALB method can be used to fabricate SLBs on a wide range of hydrophilic solid surfaces, including those which are intractable to vesicle fusion. In addition, it enables fabrication of SLBs composed of lipid compositions which cannot be prepared using the vesicle fusion method. Herein, we compare results obtained with the SALB and conventional vesicle fusion methods on two illustrative hydrophilic surfaces, silicon dioxide and gold. To optimize the experimental conditions for preparation of high quality bilayers prepared via the SALB method, the effect of various parameters, including the type of organic solvent in the deposition step, the rate of solvent exchange, and the lipid concentration is discussed along with troubleshooting tips. Formation of supported membranes containing high fractions of cholesterol is also demonstrated with the SALB method, highlighting the technical capabilities of the SALB technique for a wide range of membrane configurations.

Biomembrane Fabrication by the Solvent-assisted Lipid Bilayer SALB Method

We present an experimental protocol to form a supported lipid bilayer on solid substrates without using lipid vesicles. We demonstrate a one-step method to form a lipid bilayer on silicon dioxide and gold as well as supported membranes with cholesterol-enriched domain for various biological applications.

溶剤アシスト脂質二重（SALB）法による生体膜の作製

In order to mimic cell membranes, the supported lipid bilayer (SLB) is an attractive platform which enables in vitro investigation of membrane-related ...

Rod-based Fabrication of Customizable Soft Robotic Pneumatic Gripper Devices for Delicate Tissue Manipulation

Soft compliant gripping is essential in delicate surgical manipulation for minimizing the risk of tissue grip damage caused by high stress concentrations at the point of contact. It can be achieved by complementing traditional rigid grippers with soft robotic pneumatic gripper devices. This manuscript describes a rod-based approach that combined both 3D-printing and a modified soft lithography technique to fabricate the soft pneumatic gripper. In brief, the pneumatic featureless mold with chamber component is 3D-printed and the rods were used to create the pneumatic channels that connect to the chamber. This protocol eliminates the risk of channels occluding during the sealing process and the need for external air source or related control circuit. The soft gripper consists of a chamber filled with air, and one or more gripper arms with a pneumatic channel in each arm connected to the chamber. The pneumatic channel is positioned close to the outer wall to create different stiffness in the gripper arm. Upon compression of the chamber which generates pressure on the pneumatic channel, the gripper arm will bend inward to form a close grip posture because the outer wall area is more compliant. The soft gripper can be inserted into a 3D-printed handling tool with two different control modes for chamber compression: manual gripper mode with a movable piston, and robotic gripper mode with a linear actuator. The double-arm gripper with two actuatable arms was able to pick up objects of sizes up to 2 mm and yet generate lower compressive forces as compared to elastomer-coated and non-coated rigid grippers. The feasibility of having other designs, such as single-arm or hook gripper, was also demonstrated, which further highlighted the customizability of the soft gripper device, and it's potential to be used in delicate surgical manipulation to reduce the risk of tissue grip damage.

This protocol describes a rod-based approach, combining 3D-printing and soft lithography techniques for fabricating the soft gripper devices. This approach eliminates the need for an external air source by incorporating a chamber component and reduces the chance of occlusion during the sealing process, particularly for miniaturized pneumatic channels.

繊細な組織操作のためのカスタマイズ可能なソフトロボット空気圧グリッパ装置のロッドベースの試作

Soft compliant gripping is essential in delicate surgical manipulation for minimizing the risk of tissue grip damage caused by high stress concentrations ...

Wet Chemistry and Peptide Immobilization on Polytetrafluoroethylene for Improved Cell-adhesion

Endowing materials surface with cell-adhesive properties is a common strategy in biomaterial research and tissue engineering. This is particularly interesting for already approved polymers that have a long standing use in medicine because these materials are well characterized and legal issues associated with the introduction of newly synthesized polymers may be avoided. Polytetrafluoroethylene (PTFE) is one of the most frequently employed materials for the manufacturing of vascular grafts but the polymer lacks cell adhesion promoting features. Endothelialization, i.e., complete coverage of the grafts inner surface with a confluent layer of endothelial cells is regarded key to optimal performance, mainly by reducing thrombogenicity of the artificial interface.
This study investigates the growth of endothelial cells on peptide-modified PTFE and compares these results to those obtained on unmodified substrate. Coupling with the endothelial cell adhesive peptide Arg-Glu-Asp-Val (REDV) is performed via activation of the fluorin-containing polymer using the reagent sodium naphthalenide, followed by subsequent conjugation steps. Cell culture is accomplished using Human Umbilical Vein Endothelial Cells (HUVECs) and excellent cellular growth on peptide-immobilized material is demonstrated over a two-week period.

Cell-adhesiveness is key to many approaches in biomaterial research and tissue engineering. A step-by-step technique is presented using wet-chemistry for the surface modification of the important polymer PTFE with peptides.

改善された細胞接着のためのポリテトラフルオロエチレンにウェットケミストリーおよびペプチドの固定化

Endowing materials surface with cell-adhesive properties is a common strategy in biomaterial research and tissue engineering. This is particularly ...

Fabrication of Three-dimensional Paper-based Microfluidic Devices for Immunoassays

Paper wicks fluids autonomously due to capillary action. By patterning paper with hydrophobic barriers, the transport of fluids can be controlled and directed within a layer of paper. Moreover, stacking multiple layers of patterned paper creates sophisticated three-dimensional microfluidic networks that can support the development of analytical and bioanalytical assays. Paper-based microfluidic devices are inexpensive, portable, easy to use, and require no external equipment to operate. As a result, they hold great promise as a platform for point-of-care diagnostics. In order to properly evaluate the utility and analytical performance of paper-based devices, suitable methods must be developed to ensure their manufacture is reproducible and at a scale that is appropriate for laboratory settings. In this manuscript, a method to fabricate a general device architecture that can be used for paper-based immunoassays is described. We use a form of additive manufacturing (multi-layer lamination) to prepare devices that comprise multiple layers of patterned paper and patterned adhesive. In addition to demonstrating the proper use of these three-dimensional paper-based microfluidic devices with an immunoassay for human chorionic gonadotropin (hCG), errors in the manufacturing process that may result in device failures are discussed. We expect this approach to manufacturing paper-based devices will find broad utility in the development of analytical applications designed specifically for limited-resource settings.

We detail a method to fabricate three-dimensional paper-based microfluidic devices for use in the development of immunoassays. Our approach to device assembly is a type of multilayer, additive manufacturing. We demonstrate a sandwich immunoassay to provide representative results for these types of paper-based devices.

イムノアッセイのための3次元紙ベースのマイクロ流体デバイスの作製

Paper wicks fluids autonomously due to capillary action. By patterning paper with hydrophobic barriers, the transport of fluids can be controlled and ...

Microfluidic Platform with Multiplexed Electronic Detection for Spatial Tracking of Particles

Microfluidic processing of biological samples typically involves differential manipulations of suspended particles under various force fields in order to spatially fractionate the sample based on a biological property of interest. For the resultant spatial distribution to be used as the assay readout, microfluidic devices are often subjected to microscopic analysis requiring complex instrumentation with higher cost and reduced portability. To address this limitation, we have developed an integrated electronic sensing technology for multiplexed detection of particles at different locations on a microfluidic chip. Our technology, called Microfluidic CODES, combines Resistive Pulse Sensing with Code Division Multiple Access to compress 2D spatial information into a 1D electrical signal. In this paper, we present a practical demonstration of the Microfluidic CODES technology to detect and size cultured cancer cells distributed over multiple microfluidic channels. As validated by the high-speed microscopy, our technology can accurately analyze dense cell populations all electronically without the need for an external instrument. As such, the Microfluidic CODES can potentially enable low-cost integrated lab-on-a-chip devices that are well suited for the point-of-care testing of biological samples.

We demonstrate a microfluidic platform with an integrated surface electrode network that combines resistive pulse sensing (RPS) with code division multiple access (CDMA), to multiplex detection and sizing of particles in multiple microfluidic channels.

粒子の空間追跡のための多重化された電子の検出とマイクロ流体プラットフォーム

Microfluidic processing of biological samples typically involves differential manipulations of suspended particles under various force fields in order to ...

Fabrication and Validation of an Organ-on-chip System with Integrated Electrodes to Directly Quantify Transendothelial Electrical Resistance

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful research tools for studying human health and disease. To characterize the barrier function of cell layers cultured inside organ-on-chip devices, often transendothelial or transepithelial electrical resistance (TEER) is measured. To this end, electrodes are usually integrated into the chip by micromachining methods to provide more stable measurements than is achieved with manual insertion of electrodes into the inlets of the chip. However, these electrodes frequently hamper visual inspection of the studied cell layer or require expensive cleanroom processes for fabrication. To overcome these limitations, the device described here contains four easily integrated electrodes that are placed and fixed outside of the culture area, making visual inspection possible. Using these four electrodes the resistance of six measurement paths can be quantified, from which the TEER can be directly isolated, independent of the resistance of culture medium-filled microchannels. The blood-brain barrier was replicated in this device and its TEER was monitored to show the device applicability. This chip, the integrated electrodes and the TEER determination method are generally applicable in organs-on-chips, both to mimic other organs or to be incorporated into existing organ-on-chip systems.

This publication describes the fabrication of an organ-on-chip device with integrated electrodes for direct quantification of transendothelial electrical resistance (TEER). For validation, the blood-brain barrier was mimicked inside this microfluidic device and its barrier function was monitored. The presented methods for electrode integration and direct TEER quantification are generally applicable.

作製と内皮下電気抵抗を直接定量化する統合型電極を用いたオンチップ器官システムの検証

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful ...