This work was supported by grants from the National Institutes of Health, including a microphysiological systems consortium grant from the National Center for Advancing Translational Sciences (UH2TR000503), a Ruth L. Kirschstein National Research Service Award Postdoctoral Fellowship (F32DK098905 for WJM) and pathway to independence award (DK095984 for AB) from the National Institute of Diabetes and Digestive and Kidney Diseases.

1. Preparação da solução de colagénio nativo solúvel <ol><li> Prepare comprar ou 200 mg de acidificada, solúvel, de colagénio tipo I da cauda de ratos a 1-3 mg / 15 ml, utilizando protocolos de isolamento convencionais, tais como relatado por Piez et ai. </li><li> Escala a quantidade de material de partida com base no volume final desejado de soluções de colagénio modificados. Aproximadamente 25-30 ml de fazer metilado e 25-30 ml de soluções de colagénio succiniladas, cada um em 3 mg / ml, a partir de 200 mg de colagénio nativo solúvel. </li></ol> 2. O colágeno metilação <ol><li> Dilui-se 100 mg da solução nativa, acidificou-se (pH 2-3) de colagénio a uma concentração de 0,5 mg / ml com água estéril gelada e manter a solução em gelo para evitar a gelificação. </li><li> Ajuste o pH da solução de colagénio para 9-10 com algumas gotas de NaOH 1 N e agita-se à TA durante 30 min. Observe-se o precipitado de colagénio, fazendo com que a solução se tornar turva. </li&gt; <li> Girar a solução de colágeno precipitado a 3000 × g durante 25 min. Um precipitado claro, semelhante a gel deve ser visível no fundo dos tubos. Aspirar e descartar adequadamente o líquido sobrenadante. </li><li> Ressuspender o precipitado de colagénio em 200 ml de metanol com HCl 0,1 N e permitir que a reacção de metilação para ocorrer com agitação à temperatura ambiente durante 4 dias. O colágeno não vai dissolver, mas deve se quebrar em pedaços muito pequenos visíveis que irão tornar a solução turva. </li><li> Após a metilação, centrifugar a solução a 3000 × g durante 25 min para sedimentar o colagénio metilado. Aspirar e descarte do sobrenadante metanol acidificado. </li><li> Dissolve-se o colagénio metilado em 25 ml de PBS estéril, dando uma concentração de aproximadamente 3 mg / ml, com uma pipetagem repetida, e filtrar a solução através de um filtro de células de 60 mm. Ajuste o pH da solução para 7,3-7,4 usando 20 ul incrementos de 1 N NaOH. </li><li> Avaliar a Concentraçãn da solução utilizando um kit de ELISA comercial colágeno rato ou kit de ensaio de hidroxiprolina. Dilui-se a solução a 3 mg / ml com PBS estéril. </li><li> Esterilizar a solução de colagénio metilado, transferindo-a para um frasco de vidro com uma tampa de rosca, de camadas cuidadosamente 3 mL de clorofórmio, na parte inferior da garrafa, permitir que a garrafa para definir O / N a 4 ° C, e em seguida assepticamente remover e armazenar o camada superior, que é o colagénio metilado. </li><li> Guardar a solução a 4 ° C para utilização no prazo de 1 mês. </li></ol> 3. O colagénio succinilação <ol><li> Dilui-se a outros 100 mg da solução nativa, acidificou-se (pH 2-3) de colagénio a uma concentração de 0,5 mg / ml com água estéril gelada e manter a solução em gelo para evitar a gelificação. </li><li> Ajuste o pH da solução de colagénio para 9-10 com algumas gotas de NaOH 1 N e agita-se à TA durante 30 min. O colagénio deve precipitar, fazendo com que a solução se tornar turva. </li><li> Dissolve-se 40 mg de sucanidrido cínico (0,4 mg por mg de colagénio) em 10 ml de acetona (1/20 do volume da solução de colagénio). Lentamente (em cerca de 0,5 ml incrementos) adicionar esta mistura à solução de colagénio com agitação, enquanto se monitorizava continuamente o pH. Manter o pH acima de 9,0 através da adição de 1 ou 2 gotas de NaOH 1 N conforme o pH se aproxima de 9,0. </li><li> Continuar a agitar à temperatura ambiente durante 120 minutos após a adição de todo o anidrido succínico em acetona. Observe a solução para se tornar claro como o colágeno succinilado dissolve. Verifique periodicamente o pH para assegurar que ela permaneça acima de 9,0. </li><li> Ajustar o pH da solução para 4,0 com 20 ul incrementos de 1 N de HCl. Observar a solução turva novamente, como o colagénio precipita succinilada. </li><li> Após a succinylation, centrifugar a solução a 3000 × g durante 25 min para sedimentar o colagénio succinilado. Aspirar e descarte do sobrenadante acidificou-se com anidrido succínico não reagido. </li><li> Dissolve-se o colagénio succiniladoem 25 ml de PBS estéril, dando uma concentração de aproximadamente 3 mg / ml, com uma pipetagem repetida, e filtrar a solução através de um filtro de células de 60 mm. Ajuste o pH da solução para 7,3-7,4 usando 20 ul incrementos de 1 N NaOH. </li><li> Avaliar a concentração da solução, utilizando um kit de ELISA comercial de rato de colagénio ou kit de ensaio de hidroxiprolina. Dilui-se a solução a 3 mg / ml com PBS estéril. </li><li> Esterilizar a solução de colagénio succinilado, transferindo-a para um frasco de vidro com uma tampa de rosca, de camadas cuidadosamente 3 mL de clorofórmio, na parte inferior da garrafa, permitir que a garrafa para definir O / N a 4 ° C, e em seguida assepticamente remover e armazenar o camada superior, que é o colagénio succinilado. </li><li> Guardar a solução a 4 ° C para utilização no prazo de 1 mês. </li></ol> 4. Verificação do colagénio Modificações <ol><li> Preparar amostras de 1 ml a partir de cada uma das soluções de colagénio nativo, metilados, e succiniladas e diluir para um coneentration de 0,1 mg / ml com água pura esterilizada para titulação de íons de hidrogênio. Diluir o tampão de pelo menos 1.000 vezes por diálise contra água através de um corte de 10 kDa membraneusing 3 mudanças de solução de pelo menos 4 horas cada. </li><li> Ajustar o pH das soluções para 7.3 com pequenas quantidades de HCl e de NaOH. Usando pH 7,3 como uma referência arbitrária, executar titulação de iões de hidrogénio em cada uma das amostras, como descrito por Tanford 16 para criar curvas de titulação para as soluções de colagénio nativo, metilados, e succinilada. </li><li> Traça-se a mudança de pH por volume de ácido adicionado em relação ao número de iões H + ligada por molécula. O pH elevado &quot;amino&quot; intervalo deve mostrar uma mudança no colagénio succinilado em direcção ao ponto neutro (uma perda de grupos amina), e o pH baixo &quot;carboxilo&quot; intervalo deve mostrar um deslocamento para a esquerda no colagénio desnaturado (uma perda de grupos carboxilo ) e um desvio para a direita na colagénio succinilada (um ganho no grupo carboxilos), em comparação com o colagénio nativo. </li><li> Avaliar a eficácia da reacção succinylation pela determinação da% de grupos amino no colagénio nativa substituído por succinylation usando o método colorimétrico de ácido 2,4,6-trinitrobenzenossulfónico (TNBA), seguindo protocolos padrão 17,18. </li></ol> 5. fabricação de dispositivos microfluídicos e propagação de celular <ol><li> Fabricar dispositivos microfluídicos usando métodos padrão 9. Use réplica moldagem de PDMS de SU-8 mestres de silício definido usando fotolitografia para criar câmaras de cultura de células de microfluidos com 100 um de altura, 0,4-1,5 mm de largura e 1-10 mm de comprimento canais para o crescimento celular. </li><li> Use um limpador de plasma para oxidar as superfícies do dispositivo e uma lâmina de vidro, em seguida, pressione em conjunto para ligação. Após a esterilização do dispositivo em caso de exposição à luz UV durante pelo menos 30 min, encher a câmara com 50 ug / ml de fibronectina em PBS estéril e incubar a 37 ° C durante 45 min. </li&gt; <li> Semear o dispositivo com as células, tais como de rato primária ou hepatócitos humanos, que necessitem de um gel de colagénio para a estabilização do fenótipo ou do estado de diferenciação. Usamos 20 ul de recém-isolados hepatócitos primários de rato 7,19 comercialmente disponíveis ou criopreservados hepatócitos humanos primários semeadas a 14 x 10 6 células / ml para cada dispositivo. </li><li> Permitir que as células para anexar para 4-6 horas, e, em seguida, lavar a células não ligadas e substituir a mídia chapeamento com meios de crescimento. Incubar O / N para assegurar célula completa divulgação e criar uma monocamada confluente de células. </li></ol> 6. Camada por camada de colágeno Deposição <ol><li> Em um fluxo laminar capuz de cultura de tecidos, volumes suficientes de preparar soluções de colagénio desnaturado e succiniladas de 10 aplicações de solução por cada dispositivo, bem como de alguns ml de meio. Mantenha as soluções no gelo. Nós usamos 20 jul (10-15 vezes o volume total de dispositivo) de colágeno por camada por dispositivo. </li><li> Serdescaroçamento com a solução metilado (policatiónico), suplente rubor os dispositivos com 20 l de metilado e depois succinilado soluções de colágeno, esperando 1 min entre cada aplicação. Lave o dispositivo de um total de 10 vezes por solução, que deve levar cerca de 20 min. Trabalhar rapidamente para minimizar a quantidade de tempo que as células são sem meios. </li><li> Observar colagénio lentamente acumulam à entrada / saída em função do tamanho. Se a resistência ao fluxo do fluido aumenta, lave o dispositivo uma ou duas vezes com a mídia, e depois continuar estratificação. </li><li> Após a aplicação de todas as camadas, lavar duas vezes com o dispositivo de meios frescos e retornar para a incubadora. Dependendo do tipo de célula, as alterações morfológicas induzidas extracelulares da matriz, tais como a polarização aumentada em hepatócitos, deve ser visível dentro de algumas horas. </li><li> Prepare dispositivos representativos para microscopia electrónica de transmissão usando métodos padrão de 9 para verificar a presença de uma matriz de colagénioa montagem no topo das células cultivadas. </li></ol> 7. Estabilização do fenótipo celular e função <ol><li> Imagem da morfologia celular, viabilidade, e a polaridade usando métodos padrão para o tipo de célula. Para hepatócitos, coletar imagens ao longo de 14 dias, utilizando microscopia de fase, coloração Live / Dead para a viabilidade, e corante CMFDA para a polarização apical para demonstrar os efeitos da deposição de colágeno. </li><li> Para a morfologia das células, lave o dispositivo através da entrada, com uma pipeta, com 20 ul de PBS para enxaguar, injectar 20 ul de PBS, e a imagem do dispositivo usando microscopia de contraste de fase. </li><li> Para a coloração Live / Dead, irrigue o dispositivo através da entrada com uma pipeta com 20 l de PBS para lavar, injetar 20 ml de solução de coloração Live / Dead com DAPI preparado seguindo as instruções do fabricante, incubar por 30 min a 37 ° C, lavar a Dispositivo de novo com 20 ul de PBS, e a imagem do dispositivo usando a microscopia de fluorescência. </li><li> Para bile canalicoloração Culi, lave o dispositivo através da entrada, com uma pipeta, com 20 ul de PBS para enxaguar, injectar 20 ul de 2 gotas de solução corante uM CMFDA com DAPI preparados de acordo com as instruções do fabricante, incubar durante 30 minutos a 37 ° C, lavar novamente o dispositivo com 20 ul de PBS, e a imagem do dispositivo usando microscopia de fluorescência. </li><li> Recolher os meios gastos e medir produtos metabólicos celulares em pontos de tempo apropriados ao longo da duração da cultura para determinar a função das células. Para hepatócitos, medir a quantidade de albumina e ureia na mídia gastos. </li><li> Realizar análises funcionais de ponto final nas próprias células, como as que avaliam os níveis de enzimas de atividade, coloração de anticorpos, ou análise de RNA. Para hepatócitos, induzir e medir a atividade das enzimas do citocromo P450 ou fase II conjugação enzima glutationa S-transferase. </li></ol>

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The authors have nothing to disclose.

Ultrafinos assembleias de colágeno puro pode ser depositado em células carregadas ou superfícies de material usando deposição de camada por camada de colágenos modificados. Os resultados deste estudo demonstram que a metilação e succinylation de colagénio nativo criar soluções policatiónicos e polianiónicos de colagénio (Figura 1) que pode ser utilizado com a técnica de camada-a-camada para depositar conjuntos de matriz de colagénio ultrafinos em células (Figura 2) ou o...

Although microfluidics allows for the exquisite control of the cellular microenvironment, culturing cells, especially primary cells, within microfluidic devices can be challenging. Many traditional cell culture techniques have been developed to sustain and stabilize cell function when cultured in tissue culture plates, but translating those techniques to microfluidic devices is often difficult. 
One such technique is the culture of cells on or sandwiched between collagen gels as a model of the physiological 3D cell environment.1 Type I collagen is one of the most frequently used proteins for biomaterials applications because of its ubiquity in extracellular matrix, natural abundance, robust cell attachment sites, and biocompatibility.2 Many cells benefit from 3D culture with collagen, including cancer cells3,45, microvascular endothelial cells6, and hepatocytes7, among others. While the use of collagen gels is easy in open formats, such as tissue culture plates, the limited channel dimensions and enclosed nature of microfluidic devices makes the use of liquids that gel impractical without blocking the entire channel.
To overcome this problem, we combined the layer-by-layer deposition technique8 with chemical modifications of native collagen solutions to create ultrathin collagen assemblies on top of cells cultured in microfluidic devices. These layers can stabilize cell morphology and function similar to collagen gels and can be deposited on cells in microfluidic devices without blocking the channels with polymerized matrix. The goal of this method is to modify native collagen to create polycationic and polyanionic collagen solutions and to stabilize cells in microfluidic culture by depositing thin collagen matrix assemblies onto the cells. This technique has been used to stabilize the morphology and function of primary hepatocytes in microfluidic devices.9
Although layer-by-layer deposition has previously been reported with natural and synthetic polyelectrolytes10 to cover hepatocytes in plate culture11,12 and as a seeding layer for hepatocytes in microfluidic devices13,14, this method describes the deposition of a pure collagen layer on top of hepatocytes, mimicking the 3D collagen culture techniques. In this protocol, we use hepatocytes as example cells that can be maintained using 3D collagen layers. The many other types of cells that benefit from 3D culture in collagen may similarly benefit from culture after layer-by-layer deposition of an ultrathin collagen matrix assembly.

<table border="0" cellpadding="0" cellspacing="0">
	<tbody>
		<tr>
			<td>collagen type I, rat tail</td>
			<td>Life Technologies</td>
			<td>A1048301</td>
			<td>option for concentrated rat tail collagen</td>
		</tr>
		<tr>
			<td>collagen type I, rat tail</td>
			<td>Sigma-Aldrich</td>
			<td>C3867-1VL</td>
			<td>option for concentrated rat tail collagen</td>
		</tr>
		<tr>
			<td>collagen type I, rat tail</td>
			<td>EMD Millipore</td>
			<td>08-115</td>
			<td>option for concentrated rat tail collagen</td>
		</tr>
		<tr>
			<td>collagen type I, rat tail</td>
			<td>R%D Systems</td>
			<td>3440-100-01</td>
			<td>option for concentrated rat tail collagen</td>
		</tr>
		<tr>
			<td>succinic anhydride</td>
			<td>Sigma-Aldrich</td>
			<td>239690-50G</td>
			<td>succinylation reagent</td>
		</tr>
		<tr>
			<td>anhydrous methanol</td>
			<td>Sigma-Aldrich</td>
			<td>322415-100ML</td>
			<td>methylation reagent</td>
		</tr>
		<tr>
			<td>sodium hydroxide</td>
			<td>Sigma-Aldrich</td>
			<td>S5881-500G</td>
			<td>pH precipitation reagent</td>
		</tr>
		<tr>
			<td>hydrochloric acid</td>
			<td>Sigma-Aldrich</td>
			<td>320331-500ML</td>
			<td>pH precipitation reagent</td>
		</tr>
		<tr>
			<td>rat collagen type I ELISA</td>
			<td>Chondrex</td>
			<td>6013</td>
			<td>option for detecting collagen content</td>
		</tr>
		<tr>
			<td>hydroxyproline assay kit</td>
			<td>Sigma-Aldrich</td>
			<td>MAK008-1KT</td>
			<td>option for detecting collagen content</td>
		</tr>
		<tr>
			<td>hydroxyproline assay kit</td>
			<td>Quickzyme Biosciences</td>
			<td>QZBtotcol1</td>
			<td>option for detecting collagen content</td>
		</tr>
	</tbody>
</table>

layer-by-layer collagen deposition in microfluidic devices for microtissue stabilization

Although microfluidics provides exquisite control of the cellular microenvironment, culturing cells within microfluidic devices can be challenging. 3D culture of cells in collagen type I gels helps to stabilize cell morphology and function, which is necessary for creating microfluidic tissue models in microdevices. Translating traditional 3D culture techniques for tissue culture plates to microfluidic devices is often difficult because of the limited channel dimensions. In this method, we describe a technique for modifying native type I collagen to generate polycationic and polyanionic collagen solutions that can be used with layer-by-layer deposition to create ultrathin collagen assemblies on top of cells cultured in microfluidic devices. These thin collagen layers stabilize cell morphology and function, as shown using primary hepatocytes as an example cell, allowing for the long term culture of microtissues in microfluidic devices.

Colagénio nativo pode ser modificado usando metilação e succinylation para criar soluções de colagénio policatiónicos e polianiónicos para uso na deposição de camada por camada. Succinylation modifica os grupos e-amino de colagénio nativo com grupos succinilo, metilação e modifica os grupos carboxilo de colagénio nativo com um grupo metilo (Figura 1A). Estas modificações às cadeias laterais de aminoácidos da proteína de colagénio alterar as curvas de titulação para pH das soluçõe...

Watch this Scientific Journal Video about Layer-by-layer Collagen Deposition in Microfluidic Devices for Microtissue Stabilization at JoVE.com

Layer-by-layer Collagen Deposition in Microfluidic Devices for Microtissue Stabilization

The creation of functional microtissues within microfluidic devices requires the stabilization of cell phenotypes by adapting traditional cell culture techniques to the limited spatial dimensions in microdevices. Modification of collagen allows the layer-by-layer deposition of ultrathin collagen assemblies that can stabilize primary cells, such as hepatocytes, as microfluidic tissue models.

Camada por camada de colágeno Deposição em microfluídicos para Microtissue Estabilização

Although microfluidics provides exquisite control of the cellular microenvironment, culturing cells within microfluidic devices can be challenging. 3D ...

layer-layer-collagen-deposition-microfluidic-devices-for-microtissue

Research

JoVE Journal

Bioengineering

9.3K visualizações.  Massachusetts General Hospital, Harvard Medical School. The creation of functional microtissues within microfluidic devices requires the stabilization of cell phenotypes by adapting traditional cell culture techniques to the limited spatial dimensions in microdevices. Modification of collagen allows the layer-by-layer deposition of ultrathin collagen assemblies that can stabilize primary cells, such as hepatocytes, as microfluidic tissue models.

Vídeo: Layer-by-layer Collagen Deposition in Microfluidic Devices for Microtissue Stabilization

Separating Beads and Cells in Multi-channel Microfluidic Devices Using Dielectrophoresis and Laminar Flow

Microfluidic devices have advanced cell studies by providing a dynamic fluidic environment on the scale of the cell for studying, manipulating, sorting and counting cells. However, manipulating the cell within the fluidic domain remains a challenge and requires complicated fabrication protocols for forming valves and electrodes, or demands specialty equipment like optical tweezers. Here, we demonstrate that conventional printed circuit boards (PCB) can be used for the non-contact manipulation of cells by employing dielectrophoresis (DEP) for bead and cell manipulation in laminar flow fields for bioactuation, and for cell and bead separation in multichannel microfluidic devices. First, we present the protocol for assembling the DEP electrodes and microfluidic devices, and preparing the cells for DEP. Then, we characterize the DEP operation with polystyrene beads. Lastly, we show representative results of bead and cell separation in a multichannel microfluidic device. In summary, DEP is an effective method for manipulating particles (beads or cells) within microfluidic devices.

Dielectrophoresis (DEP) is an effective method to manipulate cells. Printed circuit boards (PCB) can provide inexpensive, reusable and effective electrodes for contact-free cell manipulation within microfluidic devices. By combining PDMS-based microfluidic channels with coverslips on PCBs, we demonstrate bead and cell manipulation and separation within multichannel microfluidic devices.

Beads separação e Células em dispositivos multi-canal microfluídicos Usando dieletroforese e Fluxo Laminar

Microfluidic devices have advanced cell studies by providing a dynamic fluidic environment on the scale of the cell for studying, manipulating, sorting ...

Bioengenharia

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.

Simples dispositivos microfluídicos para<em&gt; In vivo</em&gt; Imaging de<em&gt; C. elegans</em&gt;,<em&gt; Drosophila</em&gt; E Zebrafish

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

Engineering 3D Cellularized Collagen Gels for Vascular Tissue Regeneration

Synthetic materials are known to initiate clinical complications such as inflammation, stenosis, and infections when implanted as vascular substitutes. Collagen has been extensively used for a wide range of biomedical applications and is considered a valid alternative to synthetic materials due to its inherent biocompatibility (i.e., low antigenicity, inflammation, and cytotoxic responses). However, the limited mechanical properties and the related low hand-ability of collagen gels have hampered their use as scaffold materials for vascular tissue engineering. Therefore, the rationale behind this work was first to engineer cellularized collagen gels into a tubular-shaped geometry and second to enhance smooth muscle cells driven reorganization of collagen matrix to obtain tissues stiff enough to be handled.
The strategy described here is based on the direct assembling of collagen and smooth muscle cells (construct) in a 3D cylindrical geometry with the use of a molding technique. This process requires a maturation period, during which the constructs are cultured in a bioreactor under static conditions (without applied external dynamic mechanical constraints) for 1 or 2 weeks. The &#8220;static bioreactor&#8221; provides a monitored and controlled sterile environment (pH, temperature, gas exchange, nutrient supply and waste removal) to the constructs. During culture period, thickness measurements were performed to evaluate the cells-driven remodeling of the collagen matrix, and glucose consumption and lactate production rates were measured to monitor the cells metabolic activity. Finally, mechanical and viscoelastic properties were assessed for the resulting tubular constructs. To this end, specific protocols and a focused know-how (manipulation, gripping, working in hydrated environment, and so on) were developed to characterize the engineered tissues.

In this work, we present a technique for the rapid fabrication of living vascular tissues by direct culturing of collagen, smooth muscle cells and endothelial cells. In addition, a new protocol for the mechanical characterization of engineered vascular tissues is described.

Engenharia 3D celularizados Colágeno Gel para Vascular Regeneração Tecidual

Synthetic materials are known to initiate clinical complications such as inflammation, stenosis, and infections when implanted as vascular substitutes. ...

Microfluidic Genipin Deposition Technique for Extended Culture of Micropatterned Vascular Muscular Thin Films

The chronic nature of vascular disease progression requires the development of experimental techniques that simulate physiologic and pathologic vascular behaviors on disease-relevant time scales. Previously, microcontact printing has been used to fabricate two-dimensional functional arterial mimics through patterning of extracellular matrix protein as guidance cues for tissue organization. Vascular muscular thin films utilized these mimics to assess functional contractility. However, the microcontact printing fabrication technique used typically incorporates hydrophobic PDMS substrates. As the tissue turns over the underlying extracellular matrix, new proteins must undergo a conformational change or denaturing in order to expose hydrophobic amino acid residues to the hydrophobic PDMS surfaces for attachment, resulting in altered matrix protein bioactivity, delamination, and death of the tissues.
Here, we present a microfluidic deposition technique for patterning of the crosslinker compound genipin. Genipin serves as an intermediary between patterned tissues and PDMS substrates, allowing cells to deposit newly-synthesized extracellular matrix protein onto a more hydrophilic surface and remain attached to the PDMS substrates. We also show that extracellular matrix proteins can be patterned directly onto deposited genipin, allowing dictation of engineered tissue structure. Tissues fabricated with this technique show high fidelity in both structural alignment and contractile function of vascular smooth muscle tissue in a vascular muscular thin film model. This technique can be extended using other cell types and provides the framework for future study of chronic tissue- and organ-level functionality.

We present a method for microfluidic deposition of patterned genipin and fibronectin on PDMS substrates, allowing extended viability of vascular smooth muscle cell-dense tissues. This tissue fabrication method is combined with previous vascular muscular thin film technology to measure vascular contractility over disease-relevant time courses.

Técnica microfluídico genipina Deposição de Cultura Extensão da micropatterned vasculares musculares Filmes Finos

The chronic nature of vascular disease progression requires the development of experimental techniques that simulate physiologic and pathologic vascular ...

Using Adhesive Patterning to Construct 3D Paper Microfluidic Devices

We demonstrate the use of patterned aerosol adhesives to construct both planar and nonplanar 3D paper microfluidic devices. By spraying an aerosol adhesive through a metal stencil, the overall amount of adhesive used in assembling paper microfluidic devices can be significantly reduced. We show on a simple 4-layer planar paper microfluidic device that the optimal adhesive application technique and device construction style depends heavily on desired performance characteristics. By moderately increasing the overall area of a device, it is possible to dramatically decrease the wicking time and increase device success rates while also reducing the amount of adhesive required to keep the device together. Such adhesive application also causes the adhesive to form semi-permanent bonds instead of permanent bonds between paper layers, enabling single-use devices to be non-destructively disassembled after use. Nonplanar 3D origami devices also benefit from the semi-permanent bonds during folding, as it reduces the likelihood that unrelated faces may accidently stick together. Like planar devices, nonplanar structures see reduced wicking times with patterned adhesive application vs uniformly applied adhesive.

We demonstrate the use of patterned aerosol adhesives to construct 3D paper microfluidic devices. This method of adhesive application forms semi-permanent bonds between layers, enabling single-use devices to be non-destructively disassembled after use and to ease folding complex nonplanar structures.

Usando Adhesive Padronização Construir 3D de papel microfluídicos

We demonstrate the use of patterned aerosol adhesives to construct both planar and nonplanar 3D paper microfluidic devices. By spraying an aerosol ...

Designing Microfluidic Devices for Studying Cellular Responses Under Single or Coexisting Chemical/Electrical/Shear Stress Stimuli

Microfluidic devices are capable of creating a precise and controllable cellular micro-environment of pH, temperature, salt concentration, and other physical or chemical stimuli. They have been commonly used for in vitro cell studies by providing in vivo like surroundings. Especially, how cells response to chemical gradients, electrical fields, and shear stresses has drawn many interests since these phenomena are important in understanding cellular properties and functions. These microfluidic chips can be made of glass substrates, silicon wafers, polydimethylsiloxane (PDMS) polymers, polymethylmethacrylate (PMMA) substrates, or polyethyleneterephthalate (PET) substrates. Out of these materials, PMMA substrates are cheap and can be easily processed using laser ablation and writing. Although a few microfluidic devices have been designed and fabricated for generating multiple, coexisting chemical and electrical stimuli, none of them was considered efficient enough in reducing experimental repeats, particular for screening purposes. In this report, we describe our design and fabrication of two PMMA-based microfluidic chips for investigating cellular responses, in the production of reactive oxygen species and the migration, under single or coexisting chemical/electrical/shear stress stimuli. The first chip generates five relative concentrations of 0, 1/8, 1/2, 7/8, and 1 in the culture regions, together with a shear stress gradient produced inside each of these areas. The second chip generates the same relative concentrations, but with five different electric field strengths created within each culture area. These devices not only provide cells with a precise, controllable micro-environment but also greatly increase the experimental throughput.

Micro-fabricated devices integrated with fluidic components provide an in vitro platform for cell studies mimicking the in vivo micro-environment. We developed polymethylmethacrylate-based microfluidic chips for studying cellular responses under single or coexisting chemical/electrical/shear stress stimuli.

Projetando microfluídicos para Estudar respostas celulares Sob único ou coexistindo Chemical / Elétrica / tensão de cisalhamento Estímulos

Microfluidic devices are capable of creating a precise and controllable cellular micro-environment of pH, temperature, salt concentration, and other ...

Multi-step Variable Height Photolithography for Valved Multilayer Microfluidic Devices

Microfluidic systems have enabled powerful new approaches to high-throughput biochemical and biological analysis. However, there remains a barrier to entry for non-specialists who would benefit greatly from the ability to develop their own microfluidic devices to address research questions. Particularly lacking has been the open dissemination of protocols related to photolithography, a key step in the development of a replica mold for the manufacture of polydimethylsiloxane (PDMS) devices. While the fabrication of single height silicon masters has been explored extensively in literature, fabrication steps for more complicated photolithography features necessary for many interesting device functionalities (such as feature rounding to make valve structures, multi-height single-mold patterning, or high aspect ratio definition) are often not explicitly outlined. 
Here, we provide a complete protocol for making multilayer microfluidic devices with valves and complex multi-height geometries, tunable for any application. These fabrication procedures are presented in the context of a microfluidic hydrogel bead synthesizer and demonstrate the production of droplets containing polyethylene glycol (PEG diacrylate) and a photoinitiator that can be polymerized into solid beads. This protocol and accompanying discussion provide a foundation of design principles and fabrication methods that enables development of a wide variety of microfluidic devices. The details included here should allow non-specialists to design and fabricate novel devices, thereby bringing a host of recently developed technologies to their most exciting applications in biological laboratories.

Multilayer microfluidic devices often involve the fabrication of master molds with complex geometries for functionality. This article presents a complete protocol for multi-step photolithography with valves and variable height features tunable to any application. As a demonstration, we fabricate a microfluidic droplet generator capable of producing hydrogel beads.

Multi-passo fotolitografia Variável Altura para Valved multicamada microfluídicos Devices

Microfluidic systems have enabled powerful new approaches to high-throughput biochemical and biological analysis. However, there remains a barrier to ...

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.

Fabricação de dispositivos microfluídicos tridimensional baseados em papel para imunoensaios

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

Polydimethylsiloxane-polycarbonate Microfluidic Devices for Cell Migration Studies Under Perpendicular Chemical and Oxygen Gradients

This paper reports a microfluidic device made of polydimethylsiloxane (PDMS) with an embedded polycarbonate (PC) thin film to study cell migration under combinations of chemical and oxygen gradients. Both chemical and oxygen gradients can greatly affect cell migration in vivo; however, due to technical limitations, very little research has been performed to investigate their effects in vitro. The device developed in this research takes advantage of a series of serpentine-shaped channels to generate the desired chemical gradients and exploits a spatially confined chemical reaction method for oxygen gradient generation. The directions of the chemical and oxygen gradients are perpendicular to each other to enable straightforward migration result interpretation. In order to efficiently generate the oxygen gradients with minimal chemical consumption, the embedded PC thin film is utilized as a gas diffusion barrier. The developed microfluidic device can be actuated by syringe pumps and placed into a conventional cell incubator during cell migration experiments to allow for setup simplification and optimized cell culture conditions. In cell experiments, we used the device to study migrations of adenocarcinomic human alveolar basal epithelial cells, A549, under combinations of chemokine (stromal cell-derived factor, SDF-1&#945;) and oxygen gradients. The experimental results show that the device can stably generate perpendicular chemokine and oxygen gradients and is compatible with cells. The migration study results indicate that oxygen gradients may play an essential role in guiding cell migration, and cellular behavior under combinations of gradients cannot be predicted from those under single gradients. The device provides a powerful and practical tool for researchers to study interactions between chemical and oxygen gradients in cell culture, which can promote better cell migration studies in more in vivo-like microenvironments.

The control of chemical and oxygen gradients is essential for cell cultures. This paper reports a polydimethylsiloxane-polycarbonate (PDMS-PC) microfluidic device capable of reliably generating combinations of chemical and oxygen gradients for cell migration studies, which can be practically utilized in biological labs without sophisticated instrumentation.

Polidimetilsiloxano-policarbonato microfluídicos para celular Estudos Migratórios Sob Perpendicular Chemical e gradientes de oxigênio

This paper reports a microfluidic device made of polydimethylsiloxane (PDMS) with an embedded polycarbonate (PC) thin film to study cell migration under ...

A Microfluidic Flow Chamber Model for Platelet Transfusion and Hemostasis Measures Platelet Deposition and Fibrin Formation in Real-time

Microfluidic models of hemostasis assess platelet function under conditions of hydrodynamic shear, but in the presence of anticoagulants, this analysis is restricted to platelet deposition only. The intricate relationship between Ca2+-dependent coagulation and platelet function requires careful and controlled recalcification of blood prior to analysis. Our setup uses a Y-shaped mixing channel, which supplies concentrated Ca2+/Mg2+ buffer to flowing blood just prior to perfusion, enabling rapid recalcification without sample stasis. A ten-fold difference in flow velocity between both reservoirs minimizes dilution. The recalcified blood is then perfused in a collagen-coated analysis chamber, and differential labeling permits real-time imaging of both platelet and fibrin deposition using fluorescence video microscopy. The system uses only commercially available tools, increasing the chances of standardization. Reconstitution of thrombocytopenic blood with platelets from banked concentrates furthermore models platelet transfusion, proving its use in this research domain. Exemplary data demonstrated that coagulation onset and fibrin deposition were linearly dependent on the platelet concentration, confirming the relationship between primary and secondary hemostasis in our model. In a timeframe of 16 perfusion min, contact activation did not take place, despite recalcification to normal Ca2+ and Mg2+ levels. When coagulation factor XIIa was inhibited by corn trypsin inhibitor, this time frame was even longer, indicating a considerable dynamic range in which the changes in the procoagulant nature of the platelets can be assessed. Co-immobilization of tissue factor with collagen significantly reduced the time to onset of coagulation, but not its rate. The option to study the tissue factor and/or the contact pathway increases the versatility and utility of the assay.

This paper describes an experimental model of hemostasis that simultaneously measures platelet function and coagulation. Platelet and fibrin fluorescence is measured in real-time, and platelet adhesion rate, coagulation rate, and onset of coagulation are determined. The model is used to determine platelet procoagulant properties under flow in concentrates for transfusion.

Um Modelo de Câmara Microfluidic Fluxo de transfusão de plaquetas e Hemostasia Medidas deposição de plaquetas e formação de fibrina em tempo real

Microfluidic models of hemostasis assess platelet function under conditions of hydrodynamic shear, but in the presence of anticoagulants, this analysis is ...