Difference between revisions of "Team:Uppsala/Project/Microfluidics"

About Microfluidics

Microfluidics is both a science and a technology that is currently an active field of academic research and study. It consists of systems that work with small volumes of fluids in the nanoliter/microliter scale, through channels ranging from tens to hundreds of micrometers in diameter. Microfluidic devices have been readily used in chemistry and molecular biology and this provides a good base for further use in life sciences. There are two essential qualities in microfluidic devices that make them attractive to life science research. Firstly, the size of the device is small which makes them ideal platforms for point-of-care diagnostics that are portable. Secondly, their small size is also convenient since the volume of the liquids required to perform complex experiments is minimal, a property that can lower the cost of reactions. Thanks to fluidic components that approach the scale of a single cell, microfluidics in cell biology increases the throughput of biological and chemical assays. Small fluidic devices can perform a wide range of experimental designs and are also able to executed fully automated computer protocols. This reduces the human error and makes experiments highly efficient andreproducible. The advantages that this field brings to life science research are proof that microfluidics shows broad potential use in medicine as well. In our project, we are using microfluidic techniques to transform bacterial and yeast cells in an efficient and more automated manner.

What we did this summer?

Our first step in fabricating a microfluidics device was to plan how it is was going to function. In this process the design of the micropattern is paramount. Generally you want the channels of the microchannels kept small and use low flow rates. These parameters together with the viscosity of the fluid combine into a dimensionless number called the Reynolds number. Microfluidic devices usually have flows with low Re numbers < 2000. When flows have low Re they are labeled laminar. For a laminar flow, properties change such as its bulk motion predictability and how species in the fluid are transported via convection/diffusion as opposed to a turbulent flow where such phenomena can be very difficult to predict. How laminar the flow in your chip will be is determined by the flow rate, the fluid's viscosity and the dimensions of the channels. When designing the channels it is important to think about the range of flow rates that can be used so that the flow inside the chip are within the laminar domain. The plan for our two chips was to utilize small volumes to minimize the amount of reagents we would need. We also wanted to make the chip itself small to keep the amount of PDMS needed for curing down. The whole work of designing our lithographic molds started in AutoCAD (AutoCAD 2015 AutoDesk), a CAD software used for drawing 2D & 3D object with scientific accuracy. Although 3D modelling software such as Blender can be used these programs tend to be more difficult to work with as they are more focused on aesthetics instead of accurate angles and lengths. Since our CAD drawings in the end was being 3D printed we needed to consider the resolution of the printer and how to best print our design. It is important that the mold is flat so that the cured PDMS chip is flat in order to achieve a good bonding between PDMS and whatever substrate used to seal the channels. We wanted to be able to easily pour the PDMS into the mold, simplifying handling of sticky uncured PDMS, and also easily remove the cured chip without the risk of tearing it. The design should also use as little printer resin as possible to keep costs and print time to a minimum. The 3D printer in the end also determines how small the microchannels can be made, in our case we chose the shortest out of plane height that the printer could print without large deviations in the actual printed height. With these requirements in mind we designed the following chips. The design consists of 4 main parts. The bottom plate 33 mm L / 22 mm W, the wall structure 10 mm height / 3 mm thick, the separate detachable wall and the lithographic pattern, please see our designs for more info. The design makes it possible to reuse the box and draw new patterns depending on the application for the cured chip. The benefits of reusing the box design are to minimize future unforeseen problems concerning how well the PDMS is curing, removing of chip form the mold and the flatness of the fabricated PDMS chip, increasing repeatability.
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We designed a pattern for a heat shock transformation chip. This pattern consisted of two larger channels that would warm the smaller channel in between by circulating hot water. The cells would be injected into the middle channel and left in the channel for 45 sec and then ejected. As with the electroporation chip our thoughts was that the heating chip design easily could be included with other types of structures on “lab in a chips”.
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In our chip design for on chip electroporation we used the T-junction that combines two incoming flows connected to the pressure resistor, zigzag pattern, that evens out the pressure in the main channel, this helps generate more evenly sized droplets. Early on during planning we decided to incorporate a droplet forming section on the chip. There are many published articles that highlights the advantages of using droplets for better control of the content in the chip (Add references). By forming two phase droplets we would be able to separate the cell suspension into tiny fractions that can be manipulated independently. (Even though our currently presented prototype does not utilize the advantages of droplets, we still wanted to try and see if we could generate evenly sized and distributed droplets as this could be used for future designs. Although our droplet generation method did not allow for single cell manipulation at least it was possible to do “few cell manipulation”). After the droplets are generated they will pass two orthogonal channels that contain electrodes on either side of the main channel. The electric field between the electrodes would electroporate the passing cells inside the droplets. Since the distance between the electrodes are very small we can use a weaker electric field and control the electroporation pulse time on the cells by varying the flow rate. This design allows for continuous electroporation as opposed to current electroporators that usually only handle one cuvette at a time. We could with this design potentially electroporate how many cells we desired by automating the process and minimizing human handling.

3D-printing

Our designs

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