Patent Application
20100104459
This invention relates to the general field of microfluidics and more particularly micropumps, and concerns a micropump actuated by droplets.
Micropumps can be used to control a fluid flow, particularly in a microchannel, and are used in many microfluidics systems.
For example, micropumps may be used in laboratories on chip, medical substance injection systems or hydraulic circuits for cooling electronic chips.
Micropumps may be actuated in different ways, for example using a piezoelectric, electrostatic, thermopneumatic or even electromagnetic device. These different actuation devices are presented in the document by D. J. Laser and J. G. Santiago entitled “A review of micropumps”, J. Micromech. Microeng., 14 (2004), R35-R64.
However, these actuation devices have some disadvantages such as the presence of deformable membranes or valves, the use of high voltages, for example for piezoelectric or electrostatic devices, or high electrical consumption for example with thermopneumatic or electromagnetic devices.
Another approach that at least partly avoids the disadvantages mentioned above, consists of activating the micropump by electrowetting, and more precisely by electrowetting on dielectric.
Thus, patent application WO2002/07503A1 describes a micropump shown in
The actuation device comprises a linear network of displacement electrodes 31(1), 31(2), 31(3) . . . integrated into the substrate and arranged in the microchannel 10 starting from the reservoir 41. A counter-electrode 43 is placed in the reservoir 41 and provides electrical contact with the conducting liquid L1. The displacement electrodes are covered by a hydrophobic dielectric layer (not shown).
A voltage generator (not shown) is connected to the displacement electrodes network 31 and to the counter-electrode 43, and applies a voltage U between the electrodes.
The conducting liquid L1 forms an interface I1 with the fluid F1 filling the microchannel 10.
When the displacement electrode 31(i) located facing the interface I1 is activated by switching means (not shown) which on closure creates a contact between this electrode and the voltage source through a common conductor, the assembly comprising the liquid at voltage L1, dielectric layer and activated electrode 31(i) acts like a capacitor.
As indicated in the article by Berge entitled “Electrocapillarité et mouillage de films isolants par l'eau”, C. R. Acad. Sci., 317, series 2, 1993, 157-163, the contact angle θ of the liquid interface I1 is expressed according to the following relation:
where e is the thickness of the dielectric layer, ∈r is the permittivity of this layer and σ is the surface tension of the interface I1 of the liquid L1.
When an AC polarisation voltage U is used, the liquid L1 behaves like a conductor to the extent that the frequency of the polarisation voltage is significantly less than a cutoff frequency. This cutoff frequency, that depends particularly on the electrical conductivity of the liquid, is typically of the order of few tens of kilohertz (for example see the article by Mugele and Baret entitled “Electrowetting: from basics to applications”, J. Phys. Condens. Matter, 17 (2005), R705-R774). Furthermore, the frequency is preferably significantly greater than the frequency corresponding to the hydrodynamic response time of the liquid that depends on physical parameters such as the surface tension, viscosity or size of the microchannel and that is of the order of a few tens or hundreds of Hertz. The liquid response then depends on the effective value of the voltage, because the contact angle depends on the voltage in proportion to U2, according to the relation (1).
An electrostatic pressure acting on the interface I1 then arises close to the contact line, as explained in the article by Bavière et al. entitled “Dynamics of droplet transport induced by electrowetting actuation”, Microfluid Nanofluid, 4, 2008, 287-294. The liquid can then be displaced step by step on the hydrophobic surface by successive activation of electrodes 31(1), 31(2), etc. As it displaces, the liquid L1 “pushes” the fluid F1 along the microchannel 10.
However, the micropump according to prior art has some disadvantages.
The pressure force applied by the liquid on the fluid is proportional to cos θ(U). Thus, as the size of the angle θ(U) reduces, the pressure force will increase and the flow will also increase. In practice, the contact angle decreases with the increase in the polarisation voltage U up to a saturation angle that is normally between about 30° and 80°. The pressure force and therefore the fluid flow are then limited by this saturation angle.
Furthermore, the displacement length of the liquid in the microchannel corresponds to the length of the actuation electrodes network. Thus displacement of the liquid along the entire length of the microchannel requires that the network of electrodes should be extended along the entire length of the microchannel. Manufacturing then becomes particularly complex, particularly in the case in which the cross-section of the microchannel is non-rectangular, for example if it is circular, or if it includes direction changes.
The purpose of this invention is to disclose a micropump in which the pressure force is not limited by the electrowetting saturation angle, while being simpler to manufacture.
To achieve this, the purpose of the invention is a micropump to displace a fluid in a microchannel.
According to the invention, the microchannel comprises an inlet orifice and has an hydrophilic wall extending from said inlet orifice, and the micropump comprises means of displacing a liquid droplet by electrowetting on a hydrophobic surface until said droplet comes into contact with said hydrophilic wall, such that said droplet is introduced by wetting in said microchannel through said inlet orifice, causing displacement of said fluid.
Thus, the pressure force exerted by the liquid on the fluid in the microchannel is not limited by the electrowetting saturation angle, as it is in the micropump according to prior art.
According to this invention, electrowetting is used to bring liquid droplets as far as the inlet orifice of the microchannel, but it is not the micropump driving phenomenon.
The fluid flow is obtained by introducing the liquid droplet into the microchannel through the inlet orifice. This takes place naturally due the difference in wettability associated with the droplet. When the droplet is brought into contact with the hydrophilic wall through the inlet orifice, it wets the hydrophobic surface and the hydrophilic wall of the microchannel at the same time. The difference in wettability between these two surfaces causes migration of the entire droplet from the hydrophobic surface towards the hydrophilic wall. The liquid droplet then enters the microchannel and simultaneously “pushes” the fluid.
Furthermore, manufacturing of the micropump is simplified because it is no longer necessary to have electrowetting electrodes over the entire length of the microchannel.
Advantageously, the contact angle formed between said droplet and said hydrophilic wall is significantly less than the contact angle formed by electrowetting on said hydrophobic surface.
Said displacement means preferably comprise at least one displacement electrode and a counter-electrode in electrical contact with the droplet, and a voltage generator to apply a potential difference between one or several displacement electrodes and said counter-electrode.
Said displacement electrodes may be arranged along a determined path.
One of said displacement electrodes, called the contact making electrode, is advantageously arranged such that a liquid droplet recovering it is in contact with said hydrophilic wall through said inlet orifice.
Said displacement means may comprise a single displacement electrode, which is then said contact making electrode.
Said hydrophilic wall may have a nanotextured or microtextured surface.
Said hydrophilic wall may be a hydrophilic material.
Said hydrophilic wall may comprise a layer of a hydrophilic material.
Advantageously, said hydrophilic wall extends along the entire length of the microchannel.
A layer of dielectric material is preferably placed between said hydrophobic surface and said electrodes.
Advantageously, the microchannel comprises a connection portion defining an upstream portion and a downstream portion, said connection portion having a significantly larger cross section than the upstream portion.
The size of the connection portion is preferably between 5 and 50 times the size of the upstream portion.
A second fluid may be located downstream from the first fluid so as to form an interface with the first fluid, said interface being located in said connection portion.
The upstream portion may comprise a first upstream portion extending from the inlet orifice and a plurality of second elementary upstream portions arranged in parallel each communicating with said first upstream portion.
Each second elementary upstream portion may communicate with said connection portion.
Each second elementary upstream portion may at least be partially filled with said fluid.
The micropump advantageously comprises means of forming said droplet on said hydrophobic surface by electrowetting.
The droplet formation means may comprise a plurality of droplet formation electrodes, one of which is adjacent to a displacement electrode.
A second hydrophobic surface may be arranged facing the first hydrophobic surface so as to form a closed or confined device for said droplet.
Other advantages and characteristics of the invention will become clear after reading the non-limitative detailed description given below.
We will now describe embodiments of the invention as non-limitative examples with reference to the appended drawings among which:
A first embodiment of the invention is represented diagrammatically in a top view shown in
The micropump comprises a microchannel 10 at least partially filled with a fluid F1 and an actuation device used to control flow of said fluid F1 in the microchannel 10.
The longitudinal axis of the microchannel 10 is defined as being the median line of the microchannel. The longitudinal axis may be straight or curved, and it may have direction changes.
The microchannel 10 may have a convex polygonal cross-section, for example square, rectangular, hexagonal, a square section being a special case of the more general rectangular shape. It may also have a circular cross-section. The term microchannel in this description is considered in the general sense and in particular it includes the special case of the microtube with a circular cross-section. The microchannel may also be the catheter of a medicine dispenser system.
The transverse characteristic size of the microchannel 10 will be called the height. The height of a microtube refers to the diameter.
According to the invention, the microchannel 10 comprises an inlet orifice 11 through which a liquid L1 can pass from the outside of the microchannel 10 to the inside.
Preferably, the inlet orifice 11 is located at one end of the microchannel 10.
The microchannel 10 comprises a hydrophilic wall 12 that extends from said inlet orifice 11 onto part of the transverse contour, or preferably onto the entire transverse contour.
The hydrophilic wall 12 may extend over a defined length along the longitudinal axis of the microchannel, or preferably extend over the entire length of the microchannel.
The actuation device of the micropump controls flow of the fluid F1 in the microchannel 10.
It comprises means of displacing at least one droplet 51 of liquid L1 by electrowetting on a hydrophobic surface as far as the inlet orifice 11 of the microchannel 10.
In this case the displacement means comprise a single displacement electrode 31 integrated into or located on a support substrate 21 and covered by the hydrophobic surface.
The displacement electrode 31, called the contact making electrode, is arranged such that a droplet 51 of liquid L1 covering it is in contact with the hydrophilic wall 12 through said inlet orifice 11.
According to one variant not shown, a series of displacement electrodes may be arranged along a determined path terminating by a contact making electrode 31 placed so as to put a droplet 51 covering it into contact with the hydrophilic wall 12 through the inlet orifice 11 of the microchannel 10.
It will be noted that the verbs “cover”, “be located on”, and “be arranged on” do not necessarily mean direct contact in this description. Thus, the liquid droplet 51 may cover the displacement electrode 31 without there being any direct contact, because there is a hydrophobic surface between the droplet 51 and the electrode 31.
Note also that the droplet displacement means in this description are in a so-called open or non-confined configuration, in that said liquid droplets are not confined between two support substrates or two hydrophobic surfaces parallel to each other, but are supported solely on the support substrate 21.
In
The hydrophobic surface may be a layer of hydrophobic material.
Preferably, a layer of a dielectric material is arranged between the displacement electrode(s) 31 and the hydrophobic surface.
The dielectric and hydrophobic layers may be a single layer comprising these two functions, for example a parylene layer.
Preferably, a counter-electrode (not shown) is provided to make electrical contact with the liquid droplet 51. It is arranged at least facing the displacement electrode 31. This counter-electrode may be either a catenary, or a wire buried between the dielectric layer and the hydrophobic layer, or a planar electrode integrated into a cover of the micropump (such a cover is described later). In the latter case, an electrically conducting hydrophobic layer may cover the counter-electrode.
The displacement electrode 31 and the counter-electrode may be connected to a DC voltage generator (not shown) or preferably an AC voltage generator to move the droplet 51 by electrowetting as described above.
In the case of AC voltage, the frequency is advantageously between 100 Hz and 10 kHz, preferably of the order of 1 kHz, so as to keep the electrical conducting properties of the liquid and to exceed the hydrodynamic response time of the droplet 51. The response of the droplet 51 then depends on the RMS value of the voltage applied. The RMS value may vary between a few volts and a few hundred volts, for example 200V. It will preferably be of the order of a few tens of volts.
It is particularly advantageous if the micropump has droplet formation means 51 by electrowetting starting from a reservoir 41 containing said liquid L1.
As shown in
Preferably, said dielectric layer is also arranged between the hydrophobic surface and the formation electrodes 42.
A first formation electrode 42(1) is arranged approximately facing or close to the reservoir 41 containing the liquid. A second formation electrode 42(2) is adjacent to the first 42(1) and is followed by a third electrode 42(3). The third electrode 42(3) is preferably adjacent to the displacement electrode 31.
Advantageously, the counter-electrode and the voltage generator described above are common to the droplet formation means and the displacement means. The counter-electrode is then arranged such that it is also facing the formation electrodes 42.
Switching means (not shown) are provided to activate the different electrodes 42(1), 42(2), 42(3), 31 one after the other and thus firstly control the formation and secondly the displacement of the droplet as far as the inlet orifice 11 of the microchannel 10.
As shown in
Three electrodes 42(1), 42(2), 42(3) are shown in
Activation of this series of electrodes 42(1), 42(2), 42(3) causes the liquid to be spread by electrowetting starting from the reservoir droplet 53 in the form of a liquid segment 52 as shown in
This liquid segment 52 is then cut into two parts by deactivating the electrode 42(2). The result obtained is a droplet 51 as shown in
Therefore, a series of electrodes 42(1), 42(2), 42(3) is used to draw liquid L1 from the reservoir droplet 53 into a liquid segment 52 (
The micropump according to the first embodiment of the invention operates as follows with reference to
The droplet formation means are activated so as to form a droplet 51 of liquid L1 on the hydrophobic surface by electrowetting, as described above.
The displacement means are then activated to displace the droplet 51 formed as far as the inlet orifice 11 by electrowetting, and thus bring it into contact with the hydrophilic wall 12.
When the droplet is in contact with the hydrophilic wall 12 through the inlet orifice 11, it spontaneously enters the microchannel 10 by wetting. More precisely, the droplet migrates from the hydrophobic surface of the actuation device towards the hydrophilic wall 12 of the microchannel 10. In doing so, it “pushes” the fluid F1 contained in the microchannel 10 and thus assures controlled flow of the fluid.
When the droplet 51 has fully entered the microchannel 10, the procedure may be repeated. A second droplet 51 may be brought as far as the inlet orifice 11 by electrowetting and then introduced into the microchannel 10 by wetting. More precisely, the second droplet 51 coalesces with the liquid L1 already present in the microchannel 10 starting from the inlet orifice 11. The result obtained is then a larger volume droplet, part of which wets the hydrophobic surface and the other part wets the hydrophilic wall 12. The phenomenon remains exactly the same. The new droplet will move to dewet the hydrophobic surface and further wet the hydrophilic wall 12 of the microchannel 10. In doing so, it “pushes” the fluid F1 and thus causes the fluid to flow.
Therefore the micropump according to the invention has the advantage that it is not limited by the electrowetting saturation angle. The driving force is then the wetting force that appears spontaneously when the liquid droplet 51 is in contact with the hydrophilic wall 12 of the microchannel 10. This wetting force depends on the contact angle formed by the liquid L1 on the hydrophilic wall. This may be very small, for example of the order of or less than 10°. The pressure force and therefore the fluid flow in the microchannel are then greater than in the micropump according to prior art.
Furthermore, the flow of fluid F1 is assured provided that the microchannel 10 is supplied with liquid droplets 51 through the displacement means. The liquid L1 may spread in the microchannel 10 over the entire length of the hydrophilic wall 12. It is thus not necessary to have displacement electrodes 31 along the microchannel 10. Manufacturing of the micropump is then particularly simplified.
A second embodiment of the invention is shown in
Identical numeric references as in
In this embodiment, droplet formation and displacement means confine the liquid droplet.
A second hydrophobic surface 26 is arranged facing the first hydrophobic surface 22 and approximately parallel to it, and integrated into or placed on an upper cover 25.
Thus, a droplet 51 may be formed by the droplet formation means and displaced between the first and second hydrophobic surfaces 22, 26 by the displacement means.
Preferably, the counter-electrode 43 is integrated into the cover 25 or placed on it, and is covered by the second hydrophobic surface 26.
The droplet formation means are advantageously similar to those described in patent application WO2006/070162 filed in the name of the applicant.
Thus, a well 27 is formed in the upper cover 25.
This well 27 is placed at least partially facing a transfer electrode 47 that is integrated into the substrate 21 or located on it.
Beyond the transfer electrode 47, there is a reservoir electrode 46 that will define a liquid retention micro-reservoir.
The droplet formation electrodes 42 are then arranged followed by at least one displacement electrode, in other words a single electrode called a contact making electrode 31.
Note that although the dielectric layer is distinct from the hydrophobic layer 22, it is not shown in
As described in patent application WO2006/070162, the transfer electrode 47 pumps liquid from the reservoir (not shown) communicating with the well, so as to bring it close to the reservoir electrode 46.
A certain quantity of liquid may be accumulated on this reservoir electrode. It is shown in
Since the distance between the two substrates 21, is approximately constant (as can be seen in
When the transfer electrode is activated, it brings a portion of liquid located in the well 27, close to the reservoir electrode 46.
When the reservoir electrode is also activated, the liquid is transferred into the zone above the reservoir electrode 46.
If it is required to continue supplying the zone located above the reservoir electrode 46, the transfer electrode 47 and then the reservoir electrode 46 can be reactivated to continue to accumulate liquid in this reservoir zone.
A large volume of liquid 53 can thus be accumulated (
As long as the transfer electrode 47 is not activated, the liquid defined by the reservoir electrode 46 is not in contact with the well 27. The droplets that can be formed starting from the liquid stored above the reservoir electrode 46 can then be created in a calibrated manner, while using a well 27, independently of the pressure in the well, to fill the component.
Note that the two hydrophobic surfaces 22, 26 form two approximately parallel planes and do not form a microchannel. Thus, displacement of a droplet 51 does not cause displacement of all the surrounding fluid in the same direction. This surrounding fluid goes around the droplet 51 in its displacement. Thus, a droplet 51 can be brought as far as the inlet orifice 11 without introducing the surrounding fluid in the microchannel.
This arrangement means that droplets 51 can be dispensed reproducibly with a very high precision in volume. Volume variation coefficients (CV) (CV=2×standard deviation/average×100) less than 3% are typically measured.
Furthermore, the micropump according to this embodiment of the invention can give precise control over the flow of fluid F1 in the microchannel 10. The fluid F1 is “pushed” by the liquid droplet 51 over a distance that depends particularly on the volume of the droplet 51. Thus, the formation of a droplet with a calibrated volume can displace the fluid F1 over a precise distance.
In this embodiment of the invention, the distance between two hydrophobic surfaces 22, 26 is of the order of a few hundred micrometres, and preferably 100 μm. The volume of the droplets 51 obtained is between a few nanolitres and a few microlitres, for example 64 nl.
According to variants not shown, the reservoir droplet 53 located at the reservoir electrode 46 may be formed while the micropump is being manufactured. Thus, the droplet formation means do not include a well communicating with a reservoir, nor a transfer electrode, but simply a reservoir droplet located at the reservoir electrode. It is then advantageous if the cover 25 comprises a cavity at the reservoir electrode 46, so as to hold a large volume reservoir droplet.
It is also possible that the space located at the reservoir electrode 46, or said cavity, communicates with the exterior, such that the liquid can for example be introduced manually with a pipette, to reform or resupply the reservoir droplet. The space located at the reservoir electrode and said cavity when the liquid L1 is present in it, then form a reservoir.
The support substrate 21 and the cover 25 may be made of silicon or glass, polycarbonate, polymer or ceramic.
The microchannel 10 may for example be made by lithography and selective etching. It may be possible to use dry etching (gas etching, for example with SF6 in a plasma), depending on the required dimensions. Wet etching may also be used. Hydrofluoric acid or phosphoric acid etchings may be used for glass (mostly SiO2) or silicon nitrides (these etchings are selective but isotropic). Etching may be done by laser ablation or by ultrasounds. Micro-machining may also be used, particularly for polycarbonate. The microchannel 10 may also be made of a flexible molten silica capillary.
The height of the microchannel 10 is typically between a few tens of nanometres and 200 μm, and preferably between 1 μm and 100 μm, and even more preferably 30 μm. The length of the microchannel 10 may be few hundred microns to a few centimetres, for example 50 cm.
The displacement and formation electrodes 31, 42 and the transfer electrode 47 and the reservoir electrode 46, and the counter-electrode 43, may be made by deposition of a thin layer of a metal chosen from among Au, Al, ITO, Pt, Cu, Cr . . . or Al—Si alloy, using classical microelectronics microtechnologies, for example by photolithography. The electrodes 31, 42, 46, 47 are then etched according to an appropriate pattern, for example by wet etching.
The thickness of the electrodes 31, 42, 46, 47 may be between 10 nm and 1 μm, and preferably of the order of 300 nm. The length of the electrodes 31 and 42 may be between a few micrometres to a few millimetres, preferably between 50 μm and 1 mm, and preferably 800 μm. The surface area of these electrodes depends on the size of the droplets to be formed and displaced.
The spacing between adjacent electrodes may be between 1 μm and 20 μm.
Note that in the different embodiments, the droplet displacement and formation electrodes 31 and 42 may be approximately square or rectangular as shown on the figures.
However, the inter-electrode space may be curved or angular. In the case of an angular shape, the shape of the edge of an electrode may be a sawtooth approximately parallel to the edge of the adjacent electrode that has a corresponding shape. This electrode shape facilitates the passage of the liquid droplet from one electrode to the next.
As described in patent application WO2006/07162, the reservoir electrode 46 may be in the shape of a comb or half-star, or even a tip, to guarantee an electrode surface gradient. The shape of the transfer electrode 47 is adapted to the shape of the reservoir electrode 46.
A dielectric layer may cover the different electrodes 31, 42, 46, 47. It may be made of Si3N4, SiO2, in SiN, or strontium barium titanate (BST) or other materials with high permittivity such as HFO2, Al2O3, Ta2O5[29], Ta2O5—TiO2, SrTiO3 or Ba1-xSrxTiO3. The thickness of this layer may be between 100 nm and 3 μm, generally between 100 nm and 1 μm, and preferably 300 nm. The dielectric layer made of SiO2 may be obtained by thermal oxidation. A plasma enhanced chemical vapour deposition (PECVD) process is preferred to the low pressure chemical vapour deposition (LPCVD), for thermal stress reasons. The temperature of the substrate is only increased from 150° C. to 350° C. (depending on the required properties), compared with about 750° C. for the LPCVD deposit.
Finally, the hydrophobic surface 22 may be deposited on the dielectric layer. A Teflon deposit by dipping or spray or a plasma deposited SiOC deposit may be made for this purpose. A hydrophobic vapour or liquid phase silane deposit may be made. Its thickness will be between 100 nm and 5 μm, and preferably 1 μm. In particular, this layer can reduce or even eliminate hysteresis effects of the wetting angle.
In the case of a confined configuration, a hydrophobic layer 26 covers the counter-electrode 43.
The microchannel 10 is at least partially filled with fluid F1, preferably an insulating fluid that may be air, a mineral oil or silicon, a perfluorinated solvent such as FC-40 or FC-70, or an alkane like undecane.
The liquid L1 is electrically conducting and it may be an aqueous solution charged with ions, for example Cl−, K+, Na+, Ca2+, Mg2+, Zn2+, Mn2+ ions. The liquid may also be mercury, gallium, eutectic gallium or ionic liquids such as bmim PF6, bmim BF4 or tmba NTf2.
The volume of the liquid droplets 51 varies between a few nanolitres and a few microlitres, for example about 64 nl.
The fluid F1 is not miscible with the conducting liquid L1.
The hydrophilic nature of said wall 12 may be obtained using a material that is naturally hydrophilic for the substrate 21 in which the microchannel 10 is formed, such as aluminium, silica or hydrogel.
The substrate may also be a hydrated porous environment such as hydrated Nafion.
The hydrophilic wall 12 may also comprise a silica layer. In the case of a substrate 21 made of silicon, the silica layer may be obtained by thermal oxidation of the silicon.
The surface of the hydrophilic wall 12 may also be microtextured or nanotextured so as to amplify the wetting effects and increase the capillarity force as described in the publication by J. Bico et al. entitled “Wetting of textured surfaces” Colloids and Surfaces A, Physicochem. Eng. Aspects, 206 (2002), 41-46.
A surface is said to be or nanotextured or microtextured when the characteristic scale of its relief is between a few nanometres or micrometres and a few hundred nanometres or micrometres respectively. The textured surface may have a network of surface roughnesses, for example pins, pads or nanometric or micrometric grooves.
The hydrophilic or even super-hydrophilic nature of the wall is then obtained by a liquid film between the roughnesses. The thickness of this so-called impregnation film is comparable to the height of the roughnesses but is negligible relative to the characteristic size of the droplet. Thus, as explained by P.-G. de Gennes et al. in the book entitled “Capillarity and Wetting Phenomena: props, Bubbles, Pearls, Waves”, Springer, 2003, the droplet is eventually placed on a wetted surface that is a sort of patchwork of solids and liquids. Thus, the wall is highly hydrophilic in nature.
Different techniques known by those skilled in the art may be used to obtain a textured surface and are described particularly in the thesis by M. Callies Reyssat entitled “Splendeur et misère de l'effet lotus” (Splendour and misery of the lotus effect), 2007, Paris VI University.
Chemical surface treatment techniques may be used to make the wall 12 of the microchannel 10 hydrophilic. A chemical layer or a film is usually placed on the wall 12, the thickness of which may vary between a few nanometres and a few hundred microns.
For example, silanisation of a metallic oxide or semiconducting surface (for example SiO2, HfO2, ITO, TiO2, SnO2) or polymers (for example PDMS, the COC) in the vapour phase or liquid phase can make the wall of the microchannel hydrophilic. A large variety of silanes can be used to obtain a hydrophilic surface. In order to be as hydrophilic as possible, silanes preferably comprise an ionic group for example such as a carboxylate, a phosphate, a phosphonate, imidazolium, protonated amine, quaternary amine or a sulfonate. A number of these functions, the synthesis of associated molecules and surface functionalisation methods are described in patent application WO2007/088187.
For other oxide surfaces such as TiO2 or SnO2, it is advantageous to graft the molecule by phosphatation or phosphanation, to improve the strength of the layer. In this case, the group conferring the hydrophilic property may be of the same type as that described above. Preparation of such compounds and their use on surfaces are described particularly in the publication by F. Durmaz et al. entitled “New phosphates/phosphonates; A modular approach to functional sams”, European Cells and Materials, Vol. 6, Suppl. 1, 2003, 55.
These two methods described above may be used in different ways depending on the thickness of the layer to be obtained. Thus, the result in an anhydrous and only slightly concentrated environment is a thin layer a few nanometres thick. A thicker layer is obtained in the presence of water and alcohol (for example ethanol), varying from a few hundred nanometres to about a hundred microns using sol-gel type processes.
Note that a hydrophilic surface can also be obtained by grafting molecules in the polysaccharides family, as described in patent application WO2002/100559.
Polymer families can be used to obtain a strong hydrophilic layer about a few hundred nanometres thick, such as polyhydroxystyrenes.
Patent application WO2007/053326 also describes hydrophilic groups, for example silanols, introduced into a polymer matrix to be deposited to form the hydrophilic layer.
All techniques mentioned above are known by those skilled in the art, and can make the wall of the microchannel hydrophilic starting from the inlet orifice.
A third embodiment of the invention is shown on the top view in
Numeric references identical to those in
In this embodiment, the microchannel 10 may comprise a second fluid F2 downstream from the first fluid F1 so as to form an interface I2 with it. Preferably, the first and second fluids F1 and F2 are not miscible with each other.
The interface I2 is preferably located in a connection portion 17.
The connection portion 17 defines an upstream portion 13 extending from the inlet orifice 11 as far as the connection portion 17, and a downstream portion 16 that extends downstream from the connection portion 17.
The height of the connection portion 17 is significantly greater than the height of the upstream portion 13 of the microchannel. Preferably, the height is of the order of 5 to 50 times of the height of the upstream portion 13, and preferably ten times. Preferably, the height of the upstream portion 13 and the downstream portion 16 is constant.
The height of the downstream portion 16 may be identical to, or more or less than the height of the connection portion 17. In the example shown in
The presence of the connection portion 17 can reduce the effects of hysteresis of the contact angle that oppose fluid flow. These effects are inversely proportional to the height of the connection portion 17.
The droplet formation and displacement means are in a confined configuration in this figure, as described in the second embodiment and as shown in
This third embodiment of the invention has the advantage that it outputs a calibrated fluid flow F2 at the output from the downstream portion 16 of the microchannel.
A fourth embodiment of the invention is shown in
Numeric references identical to those in
In this embodiment of the invention, the inlet orifice 11 is arranged in the same plane as the displacement electrode 31 and is surrounded by it. The orifice inlet axis, in this case along k, is approximately orthogonal to the plane of the displacement electrode, in this case (i,j). Thus, a droplet 51 that covers the displacement electrode is brought into contact with the hydrophilic wall 12 through the inlet orifice 11.
In this embodiment, a connection portion 17 is placed between an upstream portion 13 and a downstream portion 16 of the microchannel.
The upstream portion 13 also comprises a first upstream portion 14 and a second upstream portion 15. The first upstream portion 14 extends from the inlet orifice 11. The second upstream portion 15 extends from the first upstream portion 14 as far as the connection portion 17. The downstream portion 16 corresponds to a third portion 16 of the microchannel.
More precisely, the second upstream portion 15 comprises a plurality of second elementary upstream channel portions 15′ arranged in parallel, each communicating with the first upstream portion 14 and with the connection portion 17.
The second elementary portions 15′ may be arranged in a hexagonal network and their diameter may be of the order of a few tens of microns, and preferably 30 μm. Preferably, each second elementary portion 15′ has a circular or hexagonal cross-section or a similar type of shape. The second elementary portions 15′ may be obtained by RIE type plasma etching of the substrate 21.
Preferably, the second elementary portions 15′ are filled with liquid L1 and/or the first fluid F1.
There may be a few hundred second elementary portions 15′, and their height (diameter) may be a few tens of microns, preferably 30 μm, and their length may be a few hundred microns, preferably 700 μm.
This parallel arrangement of the second elementary portions 15′ can give a high flow of the second fluid F2 in the downstream portion 16.
In this case, the droplet formation and displacement means are in a confined configuration like that described in the second embodiment and as shown in
A variant of the fourth embodiment of the invention is shown in
Numeric references identical to those in
In this variant, two elementary micropumps, each approximately identical to that described in the fourth embodiment, are arranged in parallel and are connected to each other firstly through a common well 27 filled with liquid L1, and secondly through a junction connecting the downstream portions 16-1 and 16-2. More precisely, the two downstream portions 16-1 and 16-2 are connected through a junction 18 so as to form only one portion 19.
The two micropumps may have means of controlling the droplet formation and displacement electrodes independently of each other.
Furthermore, the second fluids F2-1 and F2-2 manipulated by the two micropumps may be different.
Thus, the two second fluids F2-1 and F2-2 may be brought into contact at said junction of downstream portions 16-1 and 16-2, and thus create a mix, or even a two-phase flow.
The proportions of each second fluid F2-1 and F2-2 may be controlled using the electrode control means.
The first fluids F1-1 and F1-2 are advantageously identical.
Obviously, several elementary micropumps may be arranged in parallel, without the number of elementary micropumps being limited to two micropumps as described above.
Furthermore, the elementary micropumps do not have to be connected to each other at their corresponding downstream portion 16, so that their second fluid F2 can be dispensed independently.
Finally, note that if electronic programming means are associated with electrode control means in the different embodiments described above, dispensing sequences of calibrated quantities of the first or second fluid can be defined.
Furthermore, the so-called direct electrowetting phenomenon may be used in the case in which the dielectric layer is not present.
The capacitance used is then no longer the capacitance of the dielectric layer, but rather the capacitance of a double electrical layer formed in the conducting liquid L1 on the surface of the electrodes 31, 41. In this case, the applied voltages must be sufficiently low to prevent electrochemical phenomena such as electrolysis of the water.
The thickness e used in the relation between the contact angle θ and the applied voltage U, described above, is the thickness of the double layer that is of the order of a few nanometres.
It is then advantageous to add species with high permittivity into the liquid L1, for example such as zwitterionic species. This can increase the permittivity ∈r of the double layer. Examples of zwitterions that could be used may include amine sulfonates, amine phosphates, amine carbonates or amine carboxylates, and particularly sulfonate alkanes of ammonium trialkyl, sulfonate alkanes of imidazole alkyl, or sulfonate alkanes of pyridine alkyl.
| Number | Date | Country | Kind |
|---|---|---|---|
| 08 57310 | Oct 2008 | FR | national |
