经费是由美国国立卫生研究院MH - 64611和NARSAD青年研究者奖。作者还想Beagley，马克Dikopf，亚当史密斯和Ben承认他们的技术援助。

SU - 8模具制造硕士准备<ol><li>硅片衬底上的SU - 8的主人是准备使用两个步骤的标准消极抵制光刻工艺。 </li><li>被删除的硅片上的对准标记（位于外周边沿晶圆），使用这些结构的高度刀片超过实际设备结构。 </li><li>硅片，然后用异丙醇清洗和干燥后的 N 2流。与胶带厚度小于最高的器件结构的支柱取代四边晶圆对准标记。 注：如果支柱的高度超过最高的器件结构，通孔中形成的PDMS模具。 </li><li>主硅片上放置一个在室温下的热板。 </li></ol> PDMS的解决方案的准备<ol><li>四克的聚二甲基硅氧烷（PDMS）的解决方案是准备彻底搅拌1固化剂的一部分10有机硅弹性体的部分。 注意 ：请确保这两个解决方案是混合均匀，整个PDMS模具获得类似的物理性质，化学性质。 </li><li>使用真空干燥器，在PDMS的解决方案，在搅拌过程中产生的气泡被删除。 </li></ol>硅橡胶涂料和固化<ol><li>无气泡的PDMS的解决方案是慢慢配发到SU - 8的掌握，确保在配药过程中不产生气泡。 </li><li>的热点板块，然后放置在一个透明胶片上写的一端，慢慢地放在对PDMS解决方案的PDMS均匀分布到SU - 8的主。在此过程中所产生的任何气泡需要使用一个探头被删除。 [注：不要抬起的透明度，以防止产生更多的气泡。 </li><li>一个BOROFLOAT板被放置在顶部的透明度负债表，适用于均匀的压力。温柔的压力是最高的圆形结构的顶面（位于中间的通道长度和沿渠道的宽度为中心）等，很少或没有的PDMS夹着之间的透明度和SU - 8的圆形表面上应用结构。 </li><li>三个BOROFLOAT砖放置在硅片BOROFLOAT板夹心适用于顶面的圆形开口结构前，在固化过程中恒压之上。 </li><li>热板的温度，然后增加至75 ° C，在此温度下固化的PDMS为1小时。热板温度50 ° C </li><li>地砖被删除，轻轻除去留下的掌握和在它的上面涂薄的PDMS表的透明度。 </li></ol>微流体装置的建设 PDMS的表删除从主<ol><li>使用刀片对准SU - 8的主端口上灌注室的端口后的PDMS表上雕刻出灌注室的外部边界。 </li><li>的PDMS表删除，然后轻轻地从主，​​拉动沿长度的渠道，以防止硅橡胶撕裂。的PDMS负债表上放置一个微流体网络的表面朝上的透明度表。 </li><li>入口和出口，然后使用软木螟。 </li></ol> PDMS的表粘接玻璃盖玻片<ol><li>的PDMS表（含表面微流体网络）和玻璃盖玻片的粘接面，然后轻轻清洗使用3M透明胶带，放在一张透明度，并终于在O 2等离子室。 </li><li>粘接表面处理血浆165瓦，10秒等离子体处理表面的玻璃盖玻片立即保税的等离子体处理后的PDMS片表面。 注：适用于玻璃表面上的温和压力，以消除任何粘接表面之间的空气被困气泡。 </li><li>允许5分钟获得PDMS和玻璃之间的良好的粘接。 5分钟后，轻轻取出的PDMS表是用于粘接过程中的透明度。 </li><li>微流体装置被放置在氧等离子体系统，使渠道亲水。等离子体处理1分钟，在165瓦。 </li></ol>集成微流体装置和灌注室灌注腔的制备<ol><li>一个现成的，现成的灌注室的命令，入口和出口，使钻保税微流体装置和室时，上腔和设备的端口是一致的。灌注腔的底部表面涂以PDMS的获得之间的商会和微流体装置的密封。 </li><li>透明度负债表上写上热板在室温下放置。 </li><li>一克的PDMS解决方案是准备在前面所描述的过程类似。无气泡的PDMS的解决方案，然后慢慢地配发到的透明度负债表，避免产生气泡。 </li><li>灌注室，然后放置在PDMS的解决方案。 </li><li>一个BOROFLOAT板，然后放置在腔的顶部，适用于均匀的压力，并获得室底部表面上的PDMS涂层薄。 </li><li>热板的温度，然后增加至75 ° C，在此温度下固化的PDMS为1小时。 </li></ol>粘接微流体装置和灌注室<ol><li>板坯将被删除，轻轻离开背后的灌注室，并在其底部表面薄的PDMS表涂删除的透明度。使用一个刀片和一个尖锐的探针从接入端口的PDMS去除无用的PDMS被删除。 </li><li>硅橡胶表面的微流体装置和室的PDMS的底部表面，然后轻轻地清洗使用3M胶带，放在一张透明度，并最终在氧离子室放置。 </li><li> 165瓦10秒的等离子体表面处理立即保税室的PDMS涂层表面的PDMS表面的微流体装置。 注：适用于玻璃表面上的温和压力，以消除任何粘接表面之间的空气被困气泡。 </li><li>紧随在使用前，该设备是放置在氧等离子体系统，使渠道亲水。等离子体处理1分钟，在165瓦。 </li></ol>使用微流体装置，使脑切片神经化学物质的微环境<ol><li>亲水性微（微流体装置） - （灌注室）的组合充满标准学联（人工脑脊髓液）解决方案。 </li><li>免除在进气道学联解决方案的小滴，让溶液成渠道恶人。删除使用注射器从出气口左侧的任何气泡。免除在出气口大降了学联的解决方案，让被动的流体泵送从入口到微流体装置的电源插座端口。 注：应采取删除所有通道气泡，允许使用被动抽水方法流体流动。 </li><li>修复（微流体装置） - （灌注室）在平原平台组合和修复显微镜适配器平原平台。 </li><li>连接标准的入口和出口（吸）管灌注室连续灌注的脑片与标准学联解决方案。学联的解决方案是连续吸入95％O2 - 5％的CO 2。 注：调整吸痰管灌注室洗澡，保持学联稳定的水平。 </li><li>一旦灌注室充满学联解决方案，在灌注室使用滴管的大脑切片。使用探针，上述脑片在微流体装置的圆形开口的位置。一旦脑片圆形开口的位置，使用切片锚固定的大脑切片。 </li><li>微流体装置，现在可以用来揭露的大脑切片放置在灌注室和微流体网络上使用被动泵送流体的各种神经递质。 </li></ol>

<ol>
	<li>Blake, A. J., Pearce, T. M., Rao, N. S., Johnson, S. M., Williams, J. C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multilayer+PDMS+microfluidic+chamber+for+controlling+brain+slice+microenvironment.">Multilayer PDMS microfluidic chamber for controlling brain slice microenvironment.</a> Lab on a Chip. 7, 842-849 (2007).</li><li>Walker, G. M., Beebe, D. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+passive+pumping+method+for+microfluidic+devices.">A passive pumping method for microfluidic devices.</a> Lab on a Chip. 2, 131-134 (2002).</li></ol>

作者涉及生物学的不同领域表现出的微流体技术的合作是开放的。

现有的宏观或微观的脑片灌注商会在他们提供公开与神经递质的大脑切片的空间分辨率是有限的。这里展示的微流体装置的技术克服了这个限制，使用简单的微机电技术。据预计，在微流体设备制造和易于集成与现有的电设置简单，使所显示的设备技术的广泛应用。有趣的实验是不可能的前面，可以与目前的微流体装置。脑片不同的微环境，可以接触到不同的神经递质，在不同的时间尺度。目前的原型设备包括?...

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brain slice stimulation using a microfluidic network and standard perfusion chamber

我们已经证明了两个级别的微流体装置，可以很容易地与现有的电设置集成制造。两个级别的微流体装置是采用两个步骤的标准，消极抵制光刻工艺1。第一层次包含在每年年底与入口和出口微。第二个层次包含位于通道长度的中间，与通道宽度为中心沿微型圆孔。被动抽水的方法是用泵的液体，从进气口， 出气口2。集成微流体装置与现成的灌注商会，允许无缝集成与电设置。在进气道流通过对出口口岸的微流体介绍，并通​​过位于顶部的微灌注洗澡的圆形开口也难逃。因此可以接触不同的神经递质的大脑切片置于灌注室浴及以上的微流体装置的底部表面。微流体装置的微型厚度和材料的透明性玻璃盖玻片和PDMS（聚二甲基硅氧烷）]用于制造微流体装置允许的大脑切片的显微镜。微流体装置，可以介绍到大脑切片的微环境的化学刺激（包括空间和时间）调制。

Watch this Scientific Journal Video about Brain Slice Stimulation Using a Microfluidic Network and Standard Perfusion Chamber at JoVE.com

Brain Slice Stimulation Using a Microfluidic Network and Standard Perfusion Chamber

我们证明一个简单的微流体装置，可与标准的电设置综合揭露一个很好的控制方式不同的神经递质的大脑切片的微观表面加工。

脑片的刺激，利用微流控网络和标准灌注腔

We have demonstrated the fabrication of a two-level microfluidic device that can be easily integrated with existing electrophysiology setups. The ...

brain-slice-stimulation-using-microfluidic-network-standard-perfusion

Research

JoVE Journal

Biology

10.8K 次观看.  University of Illinois, Chicago. 我们证明一个简单的微流体装置，可与标准的电设置综合揭露一个很好的控制方式不同的神经递质的大脑切片的微观表面加工。

视频: Brain Slice Stimulation Using a Microfluidic Network and Standard Perfusion Chamber

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.

条块索玛的神经元和轴突的一个微流体设备制造

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

科研

生物学

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.

准备在微流体装置E18条块皮质大鼠神经元

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

CD4+ T-Lymphocyte Capture Using a Disposable Microfluidic Chip for HIV

CD4 + T淋巴细胞艾滋病毒的捕获使用一次性微流体芯片

Cell Capture Using a Microfluidic Device

细胞捕获使用一个微流体装置

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.

使用琼脂糖凝胶为基础的微流体装置的评估神经干细胞的运动

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

Trypsinizing and Subculturing Mammalian Cells

As cells reach confluency, they must be subcultured or passaged. Failure to subculture confluent cells results in reduced mitotic index and eventually in cell death. The first step in subculturing is to detach cells from the surface of the primary culture vessel by trypsinization or mechanical means. The resultant cell suspension is then subdivided, or reseeded, into fresh cultures. Secondary cultures are checked for growth and fed periodically, and may be subsequently subcultured to produce tertiary cultures. The time between passaging of cells varies with the cell line and depends on the growth rate.

As cells reach confluency, they must be subcultured or passaged. This video will demonstrate a procedure for subculturing both adherent and suspension cells.

Trypsinizing和传代的哺乳动物细胞

As cells reach confluency, they must be subcultured or passaged. Failure to subculture confluent cells results in reduced mitotic index and eventually in ...

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.

微探针：操作和使用的局部表面处理

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.

根据流量的血小板粘附和聚集，使用微流控流细胞

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

Mapping the After-effects of Theta Burst Stimulation on the Human Auditory Cortex with Functional Imaging

Auditory cortex pertains to the processing of sound, which is at the basis of speech or music-related processing1. However, despite considerable recent progress, the functional properties and lateralization of the human auditory cortex are far from being fully understood. Transcranial Magnetic Stimulation (TMS) is a non-invasive technique that can transiently or lastingly modulate cortical excitability via the application of localized magnetic field pulses, and represents a unique method of exploring plasticity and connectivity. It has only recently begun to be applied to understand auditory cortical function 2. 
An important issue in using TMS is that the physiological consequences of the stimulation are difficult to establish. Although many TMS studies make the implicit assumption that the area targeted by the coil is the area affected, this need not be the case, particularly for complex cognitive functions which depend on interactions across many brain regions 3. One solution to this problem is to combine TMS with functional Magnetic resonance imaging (fMRI). The idea here is that fMRI will provide an index of changes in brain activity associated with TMS. Thus, fMRI would give an independent means of assessing which areas are affected by TMS and how they are modulated 4. In addition, fMRI allows the assessment of functional connectivity, which represents a measure of the temporal coupling between distant regions. It can thus be useful not only to measure the net activity modulation induced by TMS in given locations, but also the degree to which the network properties are affected by TMS, via any observed changes in functional connectivity.
Different approaches exist to combine TMS and functional imaging according to the temporal order of the methods. Functional MRI can be applied before, during, after, or both before and after TMS. Recently, some studies interleaved TMS and fMRI in order to provide online mapping of the functional changes induced by TMS 5-7. However, this online combination has many technical problems, including the static artifacts resulting from the presence of the TMS coil in the scanner room, or the effects of TMS pulses on the process of MR image formation. But more importantly, the loud acoustic noise induced by TMS (increased compared with standard use because of the resonance of the scanner bore) and the increased TMS coil vibrations (caused by the strong mechanical forces due to the static magnetic field of the MR scanner) constitute a crucial problem when studying auditory processing. 
This is one reason why fMRI was carried out before and after TMS in the present study. Similar approaches have been used to target the motor cortex 8,9, premotor cortex 10, primary somatosensory cortex 11,12 and language-related areas 13, but so far no combined TMS-fMRI study has investigated the auditory cortex. The purpose of this article is to provide details concerning the protocol and considerations necessary to successfully combine these two neuroscientific tools to investigate auditory processing. 
Previously we showed that repetitive TMS (rTMS) at high and low frequencies (resp. 10 Hz and 1 Hz) applied over the auditory cortex modulated response time (RT) in a melody discrimination task 2. We also showed that RT modulation was correlated with functional connectivity in the auditory network assessed using fMRI: the higher the functional connectivity between left and right auditory cortices during task performance, the higher the facilitatory effect (i.e. decreased RT) observed with rTMS. However those findings were mainly correlational, as fMRI was performed before rTMS. Here, fMRI was carried out before and immediately after TMS to provide direct measures of the functional organization of the auditory cortex, and more specifically of the plastic reorganization of the auditory neural network occurring after the neural intervention provided by TMS. 
Combined fMRI and TMS applied over the auditory cortex should enable a better understanding of brain mechanisms of auditory processing, providing physiological information about functional effects of TMS. This knowledge could be useful for many cognitive neuroscience applications, as well as for optimizing therapeutic applications of TMS, particularly in auditory-related disorders.

Auditory processing is the basis of speech and music-related processing. Transcranial Magnetic Stimulation (TMS) has been used successfully to study cognitive, sensory and motor systems but has rarely been applied to audition. Here we investigated TMS combined with functional Magnetic Resonance Imaging to understand the functional organization of auditory cortex.

映射后的Theta突发刺激对人类听觉皮层功能成像

Auditory cortex pertains to the processing of sound, which is at the basis of speech or music-related processing1. However, despite considerable recent ...

Mechanical Stimulation of Chondrocyte-agarose Hydrogels

Articular cartilage suffers from a limited repair capacity when damaged by mechanical insult or degraded by disease, such as osteoarthritis. To remedy this deficiency, several medical interventions have been developed. One such method is to resurface the damaged area with tissue-engineered cartilage; however, the engineered tissue typically lacks the biochemical properties and durability of native cartilage, questioning its long-term survivability. This limits the application of cartilage tissue engineering to the repair of small focal defects, relying on the surrounding tissue to protect the implanted material. To improve the properties of the developed tissue, mechanical stimulation is a popular method utilized to enhance the synthesis of cartilaginous extracellular matrix as well as the resultant mechanical properties of the engineered tissue. Mechanical stimulation applies forces to the tissue constructs analogous to those experienced in vivo. This is based on the premise that the mechanical environment, in part, regulates the development and maintenance of native tissue1,2. The most commonly applied form of mechanical stimulation in cartilage tissue engineering is dynamic compression at physiologic strains of approximately 5-20% at a frequency of 1 Hz1,3. Several studies have investigated the effects of dynamic compression and have shown it to have a positive effect on chondrocyte metabolism and biosynthesis, ultimately affecting the functional properties of the developed tissue4-8. In this paper, we illustrate the method to mechanically stimulate chondrocyte-agarose hydrogel constructs under dynamic compression and analyze changes in biosynthesis through biochemical and radioisotope assays. This method can also be readily modified to assess any potentially induced changes in cellular response as a result of mechanical stimuli.

The biosynthesis of cartilaginous extracellular matrix by chondrocytes can be affected by application of mechanical stimuli. This method describes the technique of applying dynamic compressive strains to chondrocytes encapsulated in 3D constructs and the evaluation of induced changes in chondrocyte metabolism.

机械性刺激软骨细胞琼脂糖凝胶

Articular cartilage suffers from a limited repair capacity when damaged by mechanical insult or degraded by disease, such as osteoarthritis. To remedy ...