JP4927818B2 - Meander - Google Patents

Description

  The present invention relates to a microfluidic device incorporating one or more hydrophobic microchannel structures with one or more innovative microfluidic functions or units found herein, and these functionalities or units. And fluid methods or operations using

The microfluidic device of the present invention has one or more microchannel structures, each with one or more functional units of the present invention:
A. A capillary valve unit that can reduce rotation when the front of the liquid passes through a valve (kick valve) to convey the liquid separation portion downstream.

  B. Capillary valve unit that needs to maintain the acceleration of rotation to allow the front of the liquid to pass through the capillary valve (upward bending valve).

  C. Capillary stop unit (finger valve and / or finger vent).

  D. Protected capillary valve unit.

  E. A unit that separates the upper phase, typically the liquid phase, from the denser phase, typically with particulate material.

F. Detection unit All units A to F are mainly considered as centrifugal force-based microfluidic devices. Units C, D, E, and F can also be used in systems that drive liquid flow by other forces, including capillary forces.

  The terms “upper” and “higher” vs. “lower”, “upward” vs. “downward”, “inner” vs. “outer”, “above” vs. “lower”, etc. Means the location in relation to the direction of the main force used to drive the downstream transport or flow of liquid in the main part of the microchannel structure, for example in the main channel. This is because, in the case of centrifugal force based systems, the “higher” or “above” height / position (internal position) is shorter than the “lower” height / position (external position). Means that The radial distance of height / position is the shortest path from the height / position associated with the axis of rotation that rotates around to create the centrifugal force that the device uses internally. Similarly, the terms “up”, “up”, “inside”, “down”, “down”, “outside” and the like mean toward and away from the axis of rotation, respectively. “Height” is considered as the difference in radial position or distance between two heights, with the bottom height being the external / lower height.

  The terms described in the previous paragraph are simply confused with the terms “upstream” or “downstream” which means the order in which the various functional units appear in the flow path and / or the order in which the various steps of the protocol are performed. Should not be done. In other words, downstream means “after” and upstream means “before”.

  Affinity microchannel structures comprise one or more microtube / microchannel and / or microcavity systems, which have a liquid surface, primarily a valve function or inlet opening provided in the structure with a fractional portion. Once it begins to pass, the liquid will self-suction unless it is so done by the valve function and / or the vent, or unless it is so, eg by counter pressure created by air in the unvented internal range, or by other means Or affinity / wetting in the sense of further penetrating the system by capillary forces (passive). The affinity downstream of the valve function is that if desired, passive liquid transport can be resumed after the liquid surface has passed through the valve. The principle of self-suction is particularly true for the innovative units described herein and the structures / units in the dry state. Microchannels also include microtubes / microchannels that are not intended for liquid transport. These latter microtubes / microchannels are hydrophobic at least at the part that connects with the affinity part of the structure intended for liquid transport.

  That the two parts of the microchannel structure are in fluid or liquid communication with each other means that liquid is transported between the two parts.

  All patents and patent applications cited herein are hereby incorporated by reference in their entirety.

  Capillary valves are effective for controlling the transport of liquids in capillary force-based microfluidic devices. One of the main advantages is that neither this type of valve or centrifugal force requires mechanical means in the microfluidic device. A capillary valve is a liquid flow / carry stop and should not be confused with a flow restriction that allows flow but reduces flow (impedes flow). After a liquid surface breaks through a capillary valve, in principle there is nothing to prevent the ongoing flow or resumption after a stop (only if contact with the liquid is maintained).

  The use of capillary forces and surface tension stop features in the form of valves, vents, anti-wicking means, etc. for centrifugal force-based microfluidic systems, among others, is the following Gamera Biosciences and Gyros AB (Gamera Biosciences and Gyros AB): International Publication No. WO9853311, International Publication No. 0078455, International Publication No. 0187486, International Publication No. 0079285, International Publication No. 0187487, International Publication No. No. 2004058406, International Publication No. 9807019 (all Tecan Trading / Gamera Biosciences), International Publication No. 9958245, International Publication No. 0040750, International Publication No. 0147638 International Publication No. 018 No. 602, International Publication No. 0274438, International Publication No. 0275312, International Publication No. 03018198, International Publication No. 0302598, International Publication No. 04103890, International Publication No. 04103891, etc. (all gyros AB ( Gyros AB)).

  According to the Gamera / Tecan publication, when increasing the cross-sectional dimension to obtain a capillary valve in a hydrophilic microchannel, this is either a continuous increase or a sudden increase. May be. The inventors have performed the work using the microfluidic device mainly with a device replicated with plastic material. In our experience, in order to regulate the flow with a capillary valve based on an increase in cross-sectional dimensions, a rapid and clear change of the type not found in WO 987019 is required. Therefore, when manufacturing microfluidic valves based on changes in cross-sectional dimensions, conventional embossing, injection molding, and other replication techniques appear to be insufficient. This increase / change is expressed as “abrupt”, and by distinguishing between the change that causes the flow adjustment effect by the valve and the other change, the rapid change Compare with changes.

Another centrifugal force-based approach has been proposed by Abaxis. For example, U.S. Pat. No. 5,186,844, U.S. Pat. No. 5,242,606, U.S. Pat. No. 5,693,233, U.S. Pat. No. 5,160,702, and others. Reference may be made to J. Autom. Chem 17 (3) (1995) 99-104 (Schembri et al.). In the Aberxis system, a flow resistance in a channel between the containers controls the flow between the inner and outer containers. In addition, US Pat. No. 6,632,656 (Gyros AB) is compared. In some examples, the flow between the inner and outer containers is controlled by a so-called siphon. That is, the channel of interest is a type of capillary dimension that begins with the inner container by performing an inward bend (elbow) before ending within the outer container. By rotating at a sufficiently high rotational speed, centrifugal force prevents liquid from being carried to the tip of the elbow. As the rotational speed decreases and / or stops, wicking begins to transport liquid to the tip. When the rotation is resumed, this liquid transport is further assisted. The inner container is designed as a separation unit for separating suspended particulate material such as cells from a liquid such as blood. In order to safely hold the particulate material in the container, a weir that outlines between the outside and inside of the container is provided at the bottom of the container so that the particulate material stays outside when rotation is reduced or stopped To. Mixing can be achieved by accommodating two types of separation portions in the mixing chamber and performing a cycle of forward rotation and backward rotation, or a cycle of acceleration and deceleration rotation.
International Publication No. 9853311 International Publication No. 0078455 International Publication No. 0187486 International Publication No. 0079285 International Publication No. 0187487 International Publication No. 2004058406 International Publication No. 98007019 International Publication No. 9958245 International Publication No. 0040750 International Publication No. 0147638 International Publication No. 0185602 International Publication No.0274438 International Publication No. 0275312 International Publication No. 03018198 International Publication No. 030245598 International Publication No. 04103890 International Publication No. 04103891 US Pat. No. 5,186,844 US Pat. No. 5,242,606 US Pat. No. 5,693,233 US Pat. No. 5,160,702 US Pat. No. 6,632,656 International Publication No. 2002074438 US Patent No. 20040121449 International Publication No. 02074438 International Publication No. 02075312 International Publication No. 03093802 International Publication No. 03018198 International Publication No. 045247 International Publication No. 030245598 International Publication No. 04083108 International Publication No. 04083109 International Publication No. 04106926 International Publication No. 00007455 International Publication No. 00007285 International Publication No. 01087487 PCT / SE2005 / 001887 PCT / SE2006 / 000071 PCT / SE2006 / 000072 International Publication No. 9955827 International Publication No. 02057775 International Publication No. 020775776 International Publication No. 91016966 International Publication No. 030886960 International Publication No. 0056808 International Publication No. 2004016926 International Publication No. 20066009506 International Publication No. 01047637 International Publication No. 2005049976 US SN11 /? ? ? ? ? issue

Conclusion:
• The Gyros system primarily contemplates treating nl fractions of liquids containing reagents using centrifugal and / or capillary forces in hydrophilic microtubes. For example, the starting fraction containing uncharacterized entities such as the analyte may be in the μl range, for example ≦ 30 μl or ≦ 20 μl. In principle, the gravity of the earth is not important.

• The Abacis system utilizes very large volumes and dimensions along with centrifugal force and gravity. Channel wettability and capillary force are less important (except in the case of siphons described above). The starting fraction containing the uncharacterized entity and the reagent fraction is generally well above the nl range, for example ≧ 10 μl, ≧ 30 μl ≧ 30 μl. In many cases, the channels are large enough to allow liquids to enter containers without vents without the risk of air bubbles (filling and ventilation are parallel across one channel).

• The Tecan system is intermediate between the Gyros and Abacus systems.

Objective unit A of the various aspects of the invention: Technical problems and / or advantages:
In many cases, a centrifugal force-based system needs to continuously couple two capillary valves (I, II) so that liquid passing through the upper capillary valve I is collected at the lower capillary valve II. . Liquid collection at this valve II means that the liquid plug height accumulates, thus means that while liquid is collected at valve II, there is an increased risk of liquid leaking from this same valve. The risk of uncontrolled flow is also familiar to other flow functional units that require a controlled flow and is present downstream of the upper valve I. A typical example is a reaction microcavity containing a solid phase (eg, a porous bed) with a deactivated reactant under flow conditions where the reactant dissolved in the liquid enters the microcavity from valve I. .

  The inventors have arranged the valve I in the microtube I having an inlet end at a position higher than the outlet end, and further, from the valve I to a position in the microtube I lower than the inlet end. Designing the microtube to support the formation of a liquid plug that extends continuously downstream to a liquid surface has succeeded in reducing these risks. Creating the correct plug height between the liquid surface and the inlet end supports and facilitates downstream transport of the liquid. As a result, to transport liquid from the upstream microcavity I having the liquid outlet I connected to the inlet of the microtube I while reducing the risk of undesired flow through the valve (= valve II) or downstream perforated bed. It has become possible to reduce the rotational speed.

  Furthermore, it has been found that a suitable additional effect can be achieved if unit A is coupled to at least one of units B to F or if unit A comprises at least one characteristic of functional units B to F. .

Unit B: Technical issues and / or benefits:
For capillary valve manufacturing it is beneficial to have a simple way to change the rotational speed / centrifugal force that advances the liquid flow in a predetermined way during manufacturing. To solve this problem, a capillary valve is placed in the upward section of the microtube. The microtube is in fluid communication with the microcavity containing the liquid in the upstream direction of the microtube, and the upper height of the microcavity is the same as or substantially the same as the top height of the microtube. The centrifugal force / rotation speed required for liquid to break through the valve depends on the height of the valve relative to the axis of rotation. When the valve is arranged at a higher position in the upward section, a higher rotational speed is required than when the valve is arranged at a lower position.

  The inventors further have further advantages when unit B is coupled to or has at least one characteristic characteristic of at least one of the functional units A, C to F. I knew that I could achieve it.

Unit C: Technical issues and benefits:
The inventors have identified that creating a liquid plug in a downward-facing affinity microtube is relevant to the problem after the liquid has passed through the capillary valve in the microtube. The problem is that bubbles are easily created and surface transport (wicking) is faster than plug transport. By dividing the microtube into two or more microchannels (= finger) at the valve position and increasing the amount of liquid available for plug formation every time unit, these Succeeded in minimizing the problem. The microchannel starts from both sides of the stop / valve function or opens into a space common to all microchannels on both sides. The at least two microchannels are functionally equivalent in the sense that the liquid surface is destroyed in parallel through the microchannels, as defined elsewhere herein. Further improvements can be achieved if the sum of the cross-sectional areas of the microchannels is narrower than the cross-sectional area of the microtubes downstream of the microchannels. The inventors have also confirmed that a similar design is suitable for the venting function to equalize the overpressure / sub-pressure created in the microfluidic device during use.

  It is also confirmed that further improvements can be achieved if this unit is coupled to one or more characteristic characteristics of at least one of the functional units A to B, D to F, or provided with this characteristic characteristic. did.

Unit D: Technical issues and / or benefits:
Capillary valve efficiency includes materials that can adversely affect this type of valve, such as surface active materials and materials that can settle in and / or clog the microchannel It tends to decrease when it comes into contact with the liquid. The finger valve defined in unit C is particularly susceptible to clogging. It is therefore advantageous to protect the capillary valve from unwanted contact with this type of liquid.

  The inventors have achieved this type of protection by introducing an additional capillary valve function within the same microtube where the protected capillary valve is located. This additional valve is upstream of the protected valve.

  Further improvement can be achieved if unit D is coupled to or has at least one characteristic characteristic of at least one of functional units A to C, E to F. Also confirmed.

Unit E: Technical issues and / or benefits:
This unit has a separation microcavity I. A phase system having a lower phase and an upper phase is obtained by separating a liquid containing a high-density material from a light-weight material by centrifugal force inside the separation microcavity I. The dense material provides a partition between the lower phase. This may be a particulate material that is unstable in the liquid phase and has a higher density than the liquid phase, such as particles such as cells, a solid phase in the form of particles. The lighter material provides a partition between the upper phase and generally this is the liquid phase in which the material is dissolved, i.e. the liquid in which the particles are drastically reduced, for example plasma, suspension from cell culture, cell Homogenates, cell homogenates, and other biologically derived fluids containing particulate material are included. For example, International Publication No. WO2002074438 (Gyros AB), International Publication No. WO9853311 (Tecan Trading / Gamera Biosciences, US Patent No. 200401214449 (Bayer Healthcare), US Patent No. No. 5,186,844, U.S. Pat. No. 5,242,606, U.S. Pat. No. 5,693,233 and others (Abaxis), J. Oatme Chem 17 (3) (1995) 99-104 (Schembri After centrifugation, the upper phase is conveyed via the liquid outlet I onto the separation microcavity and also via the outlet microtube I to the separation microcavity II for further processing. International Publication No. 2002074438 (Gyros AB) It is proposed that the part of the black tube I that is connected to the separation microcavity by means of a capillary valve is directed slightly outward, which is in the form of a hydrophobic fracture associated with the connection. Publication No. 9853311 (Gamera Bioscience) proposes the following two variants for selectively conveying the upper plasma phase to the separation microcavity II: a) A closing valve (wax valve, FIG. 9). Alternatively, a variation in which the upper plasma height is adjusted upwards after the formation of the phase system (FIG. 10) US 20040121449 (Bayer Healthcare) is a downward facing with a hydrophilic or hydrophobic stop. An exit microconduit has proposed Avacis, a large capacity system, which has a discharge microtube I for the upper phase, in particular tangentially, or (U.S. Pat. No. 5,186,844, U.S. Pat. No. 5,242,606, U.S. Pat. No. 5,693,233, etc.) Chem (3) (1995) 99-104 (Schembri et al.)).

The inventors have identified that the microfluidic separation unit needs to be improved to do the following:
a) Prepare a sufficiently high quality particle sharpening part.

b) Integrating the preparation of liquid with depleted particles with precision measurement and / or further processing in a microfluidic device.

  High gravity / rotation speed is required to reduce the amount of particles in the liquid initially containing suspended particles, and valves and other flow functions downstream of the separation unit in the microfluidic device There is a high risk that the unit will malfunction. This malfunction may include clogging such as sedimentation and / or finger valves, perforated beds, narrow microtubes, among others. For this, reference can be made to the description of unit A above.

  The inventors have confirmed that an improvement can be achieved if the microtube I is connected to a liquid outlet I and this liquid outlet I is preferably equipped with an associated upward section next to the capillary valve. did. This preferably means that the liquid outlet I should be arranged in the upward part of the inner wall of the microcavity I. In other words, the transport direction through the liquid outlet I must be upward. According to our innovative concept, advantages can also be achieved for other transport directions through the liquid outlet I. The capillary valve may be directly associated with the liquid outlet I and is preferably a finger valve.

  We can achieve further improvements if unit D is coupled to or has at least one feature characteristic of at least one of functional units A-F, E-F. Also confirmed.

Unit F: Technical issues and / or benefits:
The microfluidic detection microcavity was for reading the results that occurred in the upstream reaction microcavity into solution, and generally the form was a microtube or chamber. In many cases, the detection microcavity contains the liquid that is pushed out by the solution entering from the reaction microcavity and also contains the molecular entity that has reacted the result. In conventional types of microfluidic detection microcavities, this type of design represents the risk that the incoming solution will mix with the liquid previously contained in the detection microcavity. This adverse effect has been found to be particularly disturbing in centrifugal force based systems. Mixing at this stage is undesirable because it reduces the concentration of the detected / detected entity.

  The inventors have identified a method suitable for centrifugal force-based microfluidic devices that reduces this type of undesirable mixing. Our proposal is to design the detection microcavity as a microtube having an inlet portion, an outlet portion, and one or more serpentine portions. The serpentine is defined between two outlets, each serpentine having at least two returns. The interval between the two returns is called the intermediate interval, and the return between the first and last return is called the intermediate return. The serpentine may be upward, in which case the main flow direction is also upward. That is, the entrance portion is located below the exit portion (upper meandering portion). Alternatively, the meandering portion may be downward, in which case the main flow direction is also downward. That is, the entrance portion is located above the exit portion (lower meandering portion).

  A microtube having a meandering portion arranged side by side and used as a distribution manifold is disclosed in International Publication No. 02074438, International Publication No. 02075312, International Publication No. 03093802, International Publication No. 03018198, International Publication No. No. 03024598, International Publication No. 045247, International Publication No. 04083108, International Publication No. 04083109, International Publication No. 04106926 (all Gyros AB). Microtubes that have an upright meandering part and are used as mixing microtubes are International Publication Nos. 00007455, 00007285, and 0108487 (all Gamera Biosciences / Gamera Biosciences). / Tecan Trading)). According to WO01087487 measurement and / or reaction can also be carried out in a meandering mixed microtube.

The present invention is a microfluidic device of the type described under the technical field and general title on microfluidic devices. A characteristic feature of the device is that at least one, two or more microchannel structures of the device comprise at least one functional unit A-F as described herein.

  For each unit there are also innovative ways of using the apparatus and / or microchannel structures and / or functional units for transporting and / or processing one or more liquid fractions of the present invention. At least one of the fractionation moieties includes the preparation, synthesis, and assay processing protocol reactants. This reactant may be an uncharacterized entity (analyte) or a reagent contained in a processed sample (fractionated part). This protocol is common in chemistry, biology, machinery, and other fields.

  Microtubes such as microtube I or II in various inventive units are part of the microchannel structure and have one inlet end and one outlet end. If not specified, the microtube is used to transport one or more fractionated portions of a liquid containing one or more of the reactants described above. A capillary stop function in the form of a capillary valve or capillary vent can be provided between the inlet end and the outlet end of the liquid carrying microtube, but only for defining a microcavity (capillary valve or vent. No branching involving other liquid-carrying microtubes, except when used). One or more vent microtubes can be connected to the liquid transport microtube. Unless otherwise noted, vent microtubes are only used to carry air / gas for the purpose of equalizing overpressure or sub-pressure created within the microchannel structure during liquid delivery and / or processing. Used for. A microcavity resonator may be provided between the end portions of the vent microtube.

  At the inlet end of the microtube directly connected to the liquid drainage portion of the microcavity, the end and outlet coincide. Therefore, a valve or vent located in or at the inlet end of the microtube directly connected to the liquid outlet of the microcavity is also located in or at the liquid outlet. Similarly, this applies to the outlet end of a microtube attached directly to the liquid inlet of the microcavity.

  This position in the case of a stop capillary valve is considered to be the position where the surface meniscus stops.

  Non-closed valves such as capillary valves also have a ventilation function.

A. A unit that supports the downward transport from the capillary valve by creating a drive liquid plug. This functional knit comprises:

a) Upstream microcavity I (4) with liquid inlet I (5) and liquid outlet I (6),
b) Microtube I (17) having an inlet end (16) and an outlet end (18), and
c) Capillary valve I (24) associated with microtube I (17).

  The upstream microcavity (4) is for holding a liquid fractionating portion defining an upper liquid level I therein. This upper liquid level is equal to or lower than the height of the uppermost part of the microcavity (4) (generally located at the height of the liquid inlet I (5)), or the liquid outlet I (6). It is above the height of.

  The device (1) and the microchannel structure (2) incorporating this unit, and the unit itself rotate around the rotation axis (3) to move the liquid in the upstream microcavity (4). It is designed to be discharged through the liquid outlet I (6) and further flow downstream through the microtube I (17). This transport is primarily due to rotation and / or hydrostatic pressure generated within the individual microchannel structures during rotation and / or centrifugal force generated by capillary forces. If there is sufficient rotation and / or hydrostatic pressure for the transfer, this is, for example, in a non-rotating or low-rotating state, in particular to a position where the liquid separation part or at least its surface meniscus is closer to the rotation axis (3). The first valve from the liquid inlet port (9, 51, 52, 53) of the moved and / or microchannel structure (1) (port (9, 51, 52, 53) = opening of the device structure) Or self-suction when moved to vents (15a, 15b, 24, 25 for 9; 54, 57 for 5151; 55 for 52; 56, 58 for 53) Sufficient capillary force to generate can be used as an aid.

  The main characteristic characteristics are shown below.

    i) The liquid outlet I (6) of the microtube I (17), and thus the inlet end (16), is closer to the axis of rotation (3) than the outlet end (18) of the microtube I.

    ii) Capillary valve I (24) is placed between a) liquid outlet I (6) or b) microtube I (17) inlet and outlet ends (16, 18 respectively).

    iii) The difference in radial distance between the liquid outlet (6) or valve I (24) of the upstream microcavity (4) and the outlet end (18) of the microtube I (17) is generally the upper liquid level I And the upper microcavity (4) and the top portion (7) of the liquid outlet I (6) or valve I (24) as well as the difference in radial distance between the liquid outlet I (6) or valve I (24) ≧ 5% of the difference in radial distance between and ≧ 10%, ≧ 50%, ≧ 100%, ≧ 200%, ≧ 500%.

  The upper liquid level I is always equal to or lower than the height of the uppermost part (7) of the microcavity (4).

  The portion of the micro tube I (17) downstream of the valve I (24) is the liquid in the micro tube (17) from the inlet end (16) of the micro tube I (17) (and the valve I (24)). It is designed to support liquid transport as a continuous liquid plug extending to the surface (surface meniscus) and below the height of the inlet end (16) of the microtube (17). Accordingly, the upper liquid level I at the start of conveyance first moves downward in the upstream microcavity (4), and then moves back / up according to the shape of the microtube I (17). Related to Meniscus. The maximum height of this plug is equal to the difference in diameter position of the inlet end (16) and outlet end (18) of the microtube I (17), but in practice the mutual dimensions of the microtubes, the type of liquid Depends on the number of elements, such as flow rate. When the meniscus exceeds the valve I (24) and the upstream tip (22) (if present), the plug extends downward and the rotational speed decreases. The required provisions for obtaining this type of plug transport depend on a number of factors: upstream microcavity, microtube I, microcavity liquid outlet dimensions, position and shape; liquid surface tension; added Capillary valve types including centrifugal force and dimensions; wettability of upstream microcavity and inner surface of microtube I, etc. Optimal combinations of numerical values for various features are shown in the drawings and elsewhere in this specification. Expansion of the microtube and / or its outlet end (18) counteracts the extension of the liquid plug. It is necessary to conduct experimental tests for each specific case. You can refer to the experimental part about this.

  The liquid inlet I (5) is typically provided at the top (7) of the upstream microcavity (4) and further in the upstream direction a liquid inlet port (5), ie an opening on the surface of the liquid introduction device. It is directly connected to the inflow microtube (8a) in communication. The inflow microtube (8a) is preferably provided with an overflow opening (10) at the same height as the liquid inlet I (5). If an overflow opening (10) is provided, this defines the top or top (7) of the upstream microcavity (4). This will be described in detail below.

  In general, the liquid inlet I (5) is located above the height of the liquid outlet I (6). Otherwise, the unit includes an appropriate valve function to prevent liquid from flowing back from the liquid inlet I after the upstream microcavity is filled to the desired height (= upper liquid level I). Yes.

  If valve I (24) is a non-closed valve such as a passive valve, a unique venting function is provided in the liquid outlet I (6) of the upstream microcavity. One or more venting functions can also be added within the upstream microcavity to prevent the formation of undesirable bubbles within the microcavity (not shown). Such other venting functions may be associated with pure gas vents or additional liquid inlets. The following can be referred to for this.

  The liquid flow that begins to drain from the liquid outlet I (6) is directed in various directions in relation to the centrifugal force at the liquid outlet I (6). This fluid direction comprises (a) downstream / outer component (outer radius component), (b) upper / inner component (inner radius component), (c) essentially tangential (horizontal) direction. Also good. Therefore, the direction of flow relative to the direction of the centrifugal force at the liquid outlet I (6) is at least partially oriented (along) in the same direction as the centrifugal force in the variant (a) and at least partly in the variant (b). In contrast, in the modification (c), it is essentially orthogonal to the centrifugal force. The angle with respect to the direction of the centrifugal force at the liquid outlet I is expressed by (α), which is 0 ° ≦ α ≦ 90 °, for example, 0 ° ≦ α ≦ 85 ° (along the centrifugal force) in the modified example (a). In example (b), 90 ° ≦ α ≦ 180 °, for example, 95 ° ≦ α ≦ 180 ° (against centrifugal force), and in modified example (c), 80 ≦ α ≦ 100 °, for example, 85 ° ≦ α ≦ 95 ° In particular, it may be 90 ° (perpendicular to the centrifugal force).

  The centrifugal force angle (α ′) between the liquid outlet I and the liquid outlet I and / or the inner wall of the opening is 0 ≦ α′90 ° in the modified example (a), for example, 10 ° ≦ α ′ ≦ 90 °, In the modified example (b), 0 ≦ α ′ ≦ 90 °, for example, 10 ≦ α ′ ≦ 90 °, and in the modified example (c), 0 ° ≦ α ′ ≦ 10 °, for example, 0 ° ≦ α ′ ≦ 5 °, particularly α It may be '= 0 °. These spacings are related to the angle seen from the inside of the microcavity and are considered lower / upper.

  The portion of the microtube I (17) adjacent to the liquid outlet I (6) of the upstream microcavity may be provided with a direction selected from a plurality of main directions passing through the liquid outlet (6). Two directions need not be the same direction.

  The microtube I (17) may be continuously directed downward, for example: a) linearly extending from the axis of rotation to the liquid outlet I / inlet end (6/16) of the microtube I (17) B) a curved line, for example, a meandering variant or a single-curve variant, such as within a stretched line. Alternatively, the microtube I (17) may include one or more upward sections (23a) and one or more downward sections (23b) with an upward or downward bend ("elbows") between the sections. A section and / or a horizontal section may be provided.

  In a particular variant, the microtube I (17) comprises one upward bend. This upward bend is between the height of the liquid outlet I (6) and the upper portion (7) of the upstream microcavity (4), typically between the liquid outlet I (6) and the upper liquid level I. Has an upper “elbows” (22) at height. In another preferred variant, the height of the upper tip (22) may be above or equal to the upper liquid level I, for example above the height of the top (7) of the upstream microcavity (4). Or may be equal to this. In the variant in this paragraph, all the parts of the microtube I (17) between the inlet end (16) and the upper tip (22) are generally continuously upwardly facing the microtube section (23a). As above, it is preferable to be located above the height of the liquid outlet I (6). Similarly, the part (23b) of the microtube I (17) located between the upper tip (22) and the outlet end (18) preferably faces continuously downward.

  The downward section, the upward section, the horizontal section, the upper bent portion, the lower bent portion, and the like are as described in the units B and C and / or as described for the related usage modes. Also good.

  Capillary valve I (22) consists of a) inlet end (16) of microtube I (17) (coincident with liquid outlet I (6)), b) inlet end (16) of microtube I (17). C) located at the outlet end (18) of the microtube I (17).

  The valve I (24) may be disposed either before or after the upper tip (22). When the microtube I (17) is a single lower section, the valve I (24) is at the height of the inlet end (16) of the microtube I (17) (the height of the liquid outlet I (6)). ) Or located below this height. If the microtube I (17) is an upper bend provided with an upper tip (22), the valve I (24) is located in the upper section (23a) of the bend as described in unit E. It is preferably located at the top. Valve I (24) may also be located in the lower section (23b). When the upper tip (22) is above the height of the upper valve I (24) or above the height of the uppermost portion (7) of the upstream microcavity (4), the valve I (24) Preferably, sufficient hydrostatic pressure is created by placing liquid on the back meniscus in the upstream microcavity (4) during use of the unit, or below the relevant one of these heights. . In general, the valve I (24) is at the height associated with the liquid outlet I (6), i.e., as part of the upper section (23a) of the upper bend (elbow) of the microtube I (17). It is arranged at the height of the uppermost part of about 25% or more between the end (16) (= liquid outlet I (6)) and the upper tip (22). The preferred associated position of the valve within this interval is preferably higher, for example at the top of 50% or more or 75% or more between the inlet end (16) and the upper tip (22). In this regard, further reference can be made to the units B, C, E and the usage modes of the units A to C, E, which are also mentioned for other related positions.

  Capillary valves within the unit, such as valve I (24), are generally based on changes in chemical and / or geometric inner surface features according to principles well known in the art. This change may be a sudden increase or decrease in the cross-sectional dimension of the microtube (lateral change) and / or a rapid increase in non-wetting of the inner surface of the hydrophilic microtube. In either case, the change is in the direction of flow. This change is generally local (breaking), for example, non-wetting / hydrophobic surface breakage occurring in a hydrophilic flow path. In this regard, reference can be made to “General about Microfluidic Devices”, as well as the background art and literature referenced therein. The valve I (24) is preferably a finger valve as defined in the units C and E in this specification.

  A valve I is provided in the microtube, and in particular if the valve I is a finger valve, the microtube I (17) may include an additional capillary valve (25) upstream of the valve I (24). it can. For this, reference can also be made to unit D. In a variant in which the upstream microcavity is a separate microcavity as described in unit E, this type of additional valve (25) is a valve I () by a material that passes through the microtube I and is separated from the liquid phase. 24) reduces the risk of contamination and / or clogging. In this regard, units D and E can be referred to.

  The cross-sectional area of the upstream microcavity (4) has a factor ≧ 1, for example ≧ 2, or ≧ 5, or ≧ 10 upstream of the liquid outlet I (6) than in the microtube I (17). Is preferably large. The cross-sectional area of the microtube I upstream of the valve I is preferably larger than the cross-sectional area downstream of the valve with a factor ≧ 1, for example ≧ 2, or ≧ 5, or ≧ 10. Such an interval is particularly true when the valve I is a capillary stop function in the shape of a finger valve as described in unit C.

  In particular, when the microcavity (4) is used to separate the higher density material in the liquid from the lower density material, the upstream microcavity (4) as described in unit E below. Can be divided into a lower part (4b) and an upper part (4a) by means of a liquid outlet I (6). In typical cases, the lower part (4b) constitutes ≧ 10% of the total volume of the upstream microcavity (4), for example ≧ 25%, or ≧ 50%, or ≧ 70%, or ≧ 80%. Can do. The exact relative volume of each part is determined by the relative volume of the phase discharged from the liquid outlet. Refer to unit E for this.

  Generally, the upstream microcavity tapers towards the height of the liquid outlet I (6) (or towards the output (6) itself), so that the cross-sectional area at this height is that of the liquid outlet I (6). It is smaller than the maximum cross-sectional area upstream. When the upstream microcavity (4) is separated into an upper part and a lower part (4a, 4b), generally, the microcavity (4) is provided with a constricted part to define the upper part (4a) and the lower part (4b). Is done. This constriction is essentially at the same height as the liquid outlet I (6) and is generally defined by a taper in the upper and / or lower part towards this height. Tapering / stenosis in this variant means that the cross-sectional area at the liquid outlet I (6) is smaller than one or both of the upper and lower parts, preferably the maximum cross-sectional area of the upper part (4a). The taper may be towards the liquid inlet I (5). For further explanation on this, reference can be made to the following and the explanation of unit E.

  The lower part (4b) (if provided) has one or more outlets (14) opened into the ambient atmosphere only for the purpose of discharging the air pushed out by the liquid entering this part (4b). Communicated with. The opening (port) (14) provided on the surface of the device for this type of outlet is higher than the liquid outlet (5) of the upstream microcavity (4) and is generally associated with the same microcavity. It is preferable to arrange at a position higher than the inflow port (9). Capillary stop function (downstream end) associated with this type of outlet (s) (14) (14) when the associated device surface opening is lower than the liquid inlet height of the upstream microcavity ( 15a) can be provided. The upper part (4a) of the upstream microcavity (4) can be used as a volumetric microcavity. See below for this. When the capillary stop function (15a) related to the ventilation function of the lower part (4b) is arranged at a position lower than the liquid outlet I (6), the accuracy of the volume measurement tends to increase. Reference may be made to unit D for further details.

  The lower part (4b) (if provided) is a separate liquid outlet I ′ (not shown) for discharging the material from the lower part after draining the contents of the upper part from the liquid outlet I and emptying it. ) May be provided. In this case, the liquid outlet I ′ is located below the liquid outlet I.

  The capillary stop function (15a) associated with the outlet for the lower part (4b) is preferably non-closed, for example in the form of a capillary valve or a capillary vent (preferably a finger vent as described in unit C). This can be compared with, for example, the unit 12 of International Publication No. WO02074438 (Gyros AB).

  The total volume of the upstream microcavity (4) is between the height of the uppermost part (7) (typically the liquid inlet I (5)) and the height of the lowermost part, typically the liquid outlet I (6). The maximum liquid volume that can be held.

The functional unit A further comprises a downstream microcavity II (20) provided with a liquid inlet II, which is in fluid communication with the outlet end of the microcavity I (17). In general, the microcavity (20) comprises one or more outlets, for example as shown below:
a) Liquid discharge arrangement II. This arrangement comprises a liquid outlet II (32) of the microcavity II (20) and a discharge microtube II (35), in which the transport of the material discharged from the microcavity is controlled. And / or
b) One or more ventilation functions.

  The transport control function of Array II is to place the constriction (33) at the liquid outlet II (32) and / or to prevent particulate material, eg, compressed porous bed particles, from escaping from the microcavity II (20). This is accomplished by including a liquid flow restriction in II and / or including valve II, generally a capillary valve. The valve II is located in the microtube II (35), generally at the liquid outlet II (32). A flow restriction in the form of a porous bed (34) can be placed in the microcavity, preferably at the outlet end thereof (WO 02075312 Gyros AB). The flow restriction may also be inherent in the design of the microtube II (35), e.g. long and / or narrow (WO03024598 Gyros AB) and / or a rough inner surface, It may be provided by including other features that support the disturbed flow, such as porous plugs, struts, and the like. The downstream microcavity (20) may also be provided with one or more additional liquid inlets (51, 52, 53) that may or may not match one or more venting functions. Each of these one, two or more additional inlets may or may not be part of the inflow arrangement, which is independent for each microchannel structure, Alternatively, a volume determination unit is provided having a volume measuring microcavity per microchannel structure, as is common to multiple microchannel structures and as further described in the outline of the microfluidic device below. .

  The liquid outlet II (32) is generally located in the lowermost part of the downstream microcavity (20), but is located at an intermediate height between the lowermost part and the uppermost part so that the downstream microcavity is lower and upper part. It can also be divided into parts. In this variant, the lower part may comprise a separate liquid outlet II 'with a valve II'. The downstream microcavity liquid inlet, liquid outlet, valve, upper and lower portions, and other designs may be as described above for the upstream microcavity.

  The liquid inlet II (21) is closer to the rotating shaft (3) than both the liquid outlet II (32) and II '(if provided).

  The liquid outlet II (32) may be in downstream fluid communication with the detection unit, for example as defined in unit F below. Between these liquid outlets, a micro tube II (35) as defined above is provided.

  As noted in the above description, microfluidic device overview, background art, and publications referenced in these sections, valve II and, if present, valve II ', are preferably passive valves. Other types of non-closed valves can also be used. One or more of these valves associated with the liquid outlet on the downstream microcavity (20) may be the finger valve described in unit C.

  A flow restriction in the form of a perforated bed (34) is generally associated with the bottom of the liquid outlet (32) of the downstream microcavity (20). This type of bed is generally used as a solid phase that interacts with reactants or contaminants present in the liquid fraction that passes through the bed. In general, the bed is in the form of a porous monolithic plug or a compression bed of porous or non-porous particles. The interaction with the reactants and contaminants occurs via reactants anchored to the solid phase material of the bed. Other types of flow regulation are generally used to obtain a controlled flow rate through the microcavity (20) and the perforated bed embedded therein. This makes it possible to control the residence time under the flow conditions of the liquid fraction passing through the microcavity, and thus the reactants that are stuck inside the microcavity (wall, porous bed, etc.) and the reaction that passes through. It is also possible to control the contact time between objects (International Publication No. 02075312 (Gyros AB) and International Publication No. 030259898 (Gyros AB)). The term “controlled dwell time” is used to mean one or two microstructures (identical devices) used in the same meaning as described in WO02075312 and WO03024598. ) For the associated microcavities in).

The radial distance between the inlet end (16) and the outlet end (18) of the microtube I (17) is ≧ 100%, eg ≧ 200%, or ≧ 500%, or 1000% of the difference of the following radial distances: Is preferably:
a) The difference in radial distance between the liquid inlet II (21) and the bottom liquid outlet (32) or capillary valve or flow restriction associated with the downstream microcavity (20). Or
b) The difference in radial distance between the upper liquid level in the downstream microcavity and the lowest liquid discharge valve (32) or capillary valve or flow restriction associated with the downstream microcavity (20).

  This is because the difference in radial distance between the inlet end (16) and the outlet end (18) of the microtube I (17) is defined by (a) or (b), for example ≧ 25% or ≧ 50 It is not excluded to be shorter than a difference of ≧ 10%, such as% or ≧ 75%. The term “upper liquid level” (= upper liquid level II) in (b) refers to the downstream microcavity (20 after the desired liquid volume has been transferred from the upstream microcavity (4) to the downstream microcavity (20). ) Means the liquid level.

  The volume less than half the height of the downstream microcavity (20) may be ≧ 50% of the total capacity of the microcavity, such as ≧ 60%, or ≧ 75%.

  In the same manner as the upstream microcavity (4), the downstream microcavity (20) may also be constricted and / or tapered.

  If both microcavities (4, 20) are tapered, at least one, two or more of the associated outflow / inlet inner walls are sharpened with respect to the transport direction (β <90 °) is formed. This angle (β) is preferably within an interval of 10 to 50 °, such as 20 to 40 ° and 25 to 35 °, and preferably about 30 °. These intervals can also be applied to pure ventilation outlets. As regards the liquid outlet and the pure vent outlet, the taper prevents the formation of bubbles during the filling of the microcavity with the liquid.

  If the microcavity (4, 20) has a constriction and / or a taper associated with the inlet / outlet (5/6, 32), the microcavity or its upper part (4a) and / or the lower part ( The maximum cross-sectional area of 4b) is generally greater than the cross-sectional area at the outlet / inlet height associated with a factor> 1, for example ≧ 1.25, or ≧ 1.5, or ≧ 3.0, or ≧ 5.0. Is also wide.

  The upper part (only if provided) of the upstream microcavity (4) and / or the downstream microcavity (20) is abbreviated in, for example, WO02074438 or WO03018198 (both are gyros AB). It may be part of a capacity defining unit such as the type described.

  In the case of the upstream microcavity (4), the previous paragraph means that the inflow microtube (8a) has an overflow opening (10) at the same height as the liquid inlet I (5). This overflow opening (10) generally terminates above or below a valve (15a, 15b, 24, 25) that may be associated with the liquid outlet (s) of the upstream microcavity (4), Downward overflow (11) Connected to microtube. The uppermost part of the upstream microcavity (4) is constricted at the height of the overflow opening (10) and / or tapers towards this height, ie likewise the liquid inlet I (5 ) And / or taper towards this height. In this regard, reference can be made to International Publication No. 02074438 and International Publication No. 02018198 (both are Gyros AB).

The downstream microcavity (20) may also have a volume defining function (not shown). This means that the microcavity has:
a) First liquid outlet. This is an overflow opening that divides the microcavity into an upper part and a lower part. The first liquid outlet is further provided with a first outlet and a first valve. The first outlet is directly connected to the overflow opening, and is designed as an overflow microtube whose outlet end is directed downward. The first valve may be above or below the height of the valve in the liquid outlet and / or the lower part of the microcavity.

b) Second liquid outlet. This is i) in the lower part of the microcavity, ii) connected to the inlet end of the second discharge microtube in downstream liquid communication with the downstream part of the microchannel structure, and iii) the second liquid outlet and / or Or associated with a second valve in the second microtube.

  In this design, the lower portion of the microcavity is associated with the volumetric microcavity and the first liquid outlet is associated with the liquid outlet II (32) in the figure. The second liquid outlet is not shown in the variant of this drawing. Valves such as the first and second valves are generally non-closed valves, and may be, for example, capillary valves that are preferably designed as considered elsewhere in this specification.

  The constriction and taper are as outlined for the relevant part in the upstream microcavity. This can be referred to above and also to unit E.

  The microchannel structure of this innovative device may comprise at least two units connected in series so that the downstream microcavity of the upstream unit can be in fluid communication with the upstream microcavity of the nearest downstream unit. This continuously coupled unit may differ in that the upstream or downstream microcavity of the upstream unit does not perform the same operation as the associated downstream unit microcavity. The downstream microcavity of the upstream unit can coincide with the upstream microcavity of the nearest downstream unit. If the upstream and downstream microcavities of two consecutive units do not match, another functional unit can be inserted between them.

  The upstream microcavity (4) may comprise: a) a mixing and / or dilution function. In this case, generally two or more liquid inlets are provided on the microcavity. b) A function of separating a material having a lower density from a material having a higher density as described in the following unit E. c) The ability to perform one or more biochemical reactions selected from reactions involving cells or parts of cells, enzymatic reactions, affinity reactions, etc. The function of the upstream microcavity (4) can be selected from the same functions (see above) as the downstream microcavity (20), and vice versa for the downstream microcavity (20). The function of the two microcavities depends on what is performed inside each. The upstream microcavity (4) may be equipped with one, two, three, or more inlets that are part of the inflow arrangement described above for the downstream microcavity (20).

  If the microcavity is designed to carry out the types of reactions listed above, these reactions may occur between dissolved reactants and / or with one or more dissolved reactants. Between the reactant / reactants associated with the solid phase within the microcavity involved. If the upstream microcavity has a separation or fractionation function as described above and in unit E, a reaction occurs in the downstream microcavity. As used in this context, the term “dissolved reactant” refers to a suspended reactant, eg, a reactant attached to a suspended particulate solid phase held in a microcavity, eg, a cell or a portion of a cell. , Including others. The term “retained” means that the solid phase is maintained in the microcavity during the reaction and after at least partial removal of the liquid present during the reaction. In general, such a solid phase has an inner wall, for example a porous bed such as a porous monolith, arranged in the downstream end of the microcavity and / or in an exhaust microtube such as microtube I, II, II ′, A packed bed of particles. If a perforated bed is associated with the outlet, there is no separate valve function associated with this outlet. The possibility of a reaction occurring in the microcavity is combined with performing mixing and / or dilution in a previous step within the same microcavity or upstream microcavity (if provided).

  One aspect of the present invention associated with unit A is the use of a microfluidic device, in which the microstructure comprises an innovative unit A. This method comprises the following steps.

  i) providing a microfluidic device (1); This device contains a microchannel structure (2) with unit A as defined above, and the upstream microcavity of the unit is filled with liquid up to the upper liquid level I. That is, the liquid level above the microtube I (17) is filled with the back meniscus and the valve I (24) is filled with the front meniscus.

  ii) moving the front meniscus so that it can pass through the valve I (24) by rotating the device (1) around the axis of rotation (3) at a certain rotational speed;

  iii) The liquid plug extends continuously from the valve I (24) into the microtube I (17) with the front meniscus moving downstream toward the outlet end (18) of the microtube I (17). So that the back meniscus can move into the microtube I (17) and, if possible, through it, the outlet end of the microtube I (17). Emptying the microcavity (4) to the liquid inlet I (5) by discharging the liquid from the upstream microcavity (4) through the section.

If the microcavity (4) has a lower first part (4b), a new meniscus is created at the height of the liquid outlet (6) in the microcavity. When the microtube I has an upper tip (22) above the upper liquid level I and the valve I (24) is positioned upstream of the upper tip (ie, below the upper liquid level I) The sequence “(ii) and (iii)” comprises the following steps:
(Ii.a) moving the front meniscus to valve I (24) by rotating the device and passing the valve through the front meniscus.

  (Ii.b) Step of keeping the liquid in an equilibrium state by rotation so that the front and back meniscuses are aligned at the same height.

  (Ii.c) Rotation is stopped if necessary so that the capillary force is greater than the centrifugal force at the front meniscus, and the upper tip until the front meniscus is below the height of the back meniscus ( 22) adjusting the rotational speed by allowing the capillary fluid transport to 22).

  (Iii ') emptying the upstream microcavity (4) to the height of the liquid outlet I (6) by discharging liquid from the outlet end (18) of the microtube I (17).

  During step (ii.b), the rotational speed is greatly increased, mainly due to the material properties of the microfluidic device only. This achieves a very efficient centrifugal force-based fractionation of low density materials from lighter materials to upper and lower phases in the upstream microcavity. Alternatively, steps (iii) and (iii ') may comprise a liquid transport that does not necessarily require a liquid plug to be continuously formed from valve I.

In one or more steps, as the drive plug height (between the front meniscus and the back meniscus) extends, the rotational speed / centrifugal force decreases continuously or decreases. This reduces the risk of undesirable and / or uncontrolled liquid delivery from the liquid outlet II (32) of the stream stream microcavity (20). This danger is caused by the increased liquid level / hydrostatic pressure caused by the liquid conveyed to the downstream microcavity (20). In an ideal case, the rotational speed and design of unit A are adapted to each other, and during the execution of at least part of the second half of the transfer, the height of the liquid in the downstream microcavity is equal to the upstream microcavity (4) and the micro For example, ≦ 0.75, ≦ 0.5, ≦ 0.25, ≦ 0.1, the factor F ≦ 1 is lower than the total driving liquid level in the pipe I (18). In an ideal case, it is desirable that this condition is satisfied throughout the entire conveyance. This method of execution steps (iii) and / or (iii ′) is supported in the following cases:
a) The height of the upstream microcavity (4) is higher than the height of the downstream microcavity (20) by a factor F ′ ≧ 1, for example, ≧ 1.5, ≧ 3, ≧ 5, ≧ 10.

b) The maximum cross-sectional area of the downstream microcavity (20), for example less than 60% in height, is larger than the maximum cross-sectional area of the upstream microcavity (4).

c) When the capacity of the downstream microcavity is larger than the capacity of the upstream microcavity (4) by a factor F ″ ≧ 1, for example, ≧ 1.5, ≧ 2, ≧ 5.

  Thereby, the height of the upstream microcavity (4) is between the height of the uppermost part (7) and the height of the lowermost liquid outlet with a capillary valve such as the liquid outlet I (6). Conceivable. According to this, the height of the downstream microcavity (20) is between the height of the liquid inlet II (21) and the lowest liquid outlet with a capillary valve, for example a liquid outlet II (32). it is conceivable that. This does not exclude the case where the height of the upstream microcavity may be less than the height of the downstream microcavity, F ′ <1, eg ≦ 0.75, ≦ 0.50, ≦ 0.25. . As described in any part of the previous description, and in the units B, C, and D, if there is an upper tip in the microtube I, the present embodiment of this part of the unit A is also supported. The

  The actual rotational speed (rotation program) required at different steps depends on a number of factors in a complex manner and is generally determined before the actual processing protocol is implemented. In the case of steps (iii) and (iii ′), the step is started at a relatively high rotational speed, and then at a certain step, the rotational speed is increased by a factor ≧ 0.10, for example ≧ 0.20 or higher. It is always advantageous to reduce the rotational speed continuously by reducing it and then reducing it over several steps or continuously more smoothly. The continuous reduction of the rotational speed is particularly advantageous when the unit is equipped with a downstream microcavity (20) with which the aforementioned capillary valve is associated.

The upstream microcavity (4) or its upstream part (4b) is a volumetric microcavity of a volume defining unit with an overflow microtube (11) coupled at the height of the liquid inlet I (5) of the upstream microcavity. May be. In this case, step (i) comprises:
a) Provide excess liquid in the upstream microcavity (4). Filling the microcavity (4a-4b) and placing excess liquid in the overflow microtube (11), dropping into the overflow valve (15b) inside it and moving to the inflow microtube (8a).

b) While the liquid remains in the upstream microcavity, the device is forced to move the liquid to the overflow microtube (11) and the discharge microtube (8a) and drain it from the overflow valve (15b). Rotating around the axis of rotation.

  This rotational speed is lower than the speed required to drain liquid from valve I (24) (and valve I '(25) if provided). This is because the valve (15b) in the overflow microtube (11) is designed to be weaker than the other liquid discharge valves associated with the upstream microcavity (24, and 25 if provided). It is. As for this, for example, International Publication No. 02075312, International Publication No. 02057775, International Publication No. 04083108 (all Gyros AB) and others can be referred to. This also means that the back meniscus after step (ii.b) may be below the liquid inlet / outlet openings (5, 10) of the upstream microcavity (4).

  As described above, the liquid outlet I (5) divides the upstream microcavity (4) into an upper part (4a) and a lower part (4b). Rotate to separate liquid containing higher density material and lower density material (lighter material) into upper phase containing lighter material and lower phase containing higher density material It can also be used to The actual separation into two phases is most efficiently performed by rotation during the above step (ii.b). Step (ii.b) means that the microtube I (17) is above the upper liquid level I in the upstream microcavity (4) (not shown) and the valve I (24) is upstream of the tip. And an upper tip (22) disposed below the upper liquid level I. In another variation of unit A, the actual separation into two phases is lower than the rotational speed required to pass liquid through valve I (24) between steps (i) and (ii). , By rotating the device at a higher speed than that used in step (i) and in many cases higher than that used in step (iii). In this method variant, the microtube I (17) has an upper tip (22) below the upper liquid level I, and a height upstream of the tip (22) and below the upper liquid level I. It is preferred that the valve I (24) is arranged in the. Centrifugation described in this paragraph consists of (1) reacting the dissolved reactant with a reactant fixed to a suspended solid phase of microparticles, and (2) a cell culture suspension, A sample containing a cell or part of a cell, such as a cell homogenate, whole blood, etc. In this regard, reference can also be made to the description and use of unit E.

B. Functional unit with capillary valve in upward microtube This unit is a liquid carrying microtube I (17 with an inlet end (16) and outlet end (18) and a capillary valve I between both ends. ).

  A characteristic characteristic is that the microtube I (17) has an upward section (23a) extending partly or entirely. In a preferred variant, the capillary valve I (24) is in this upward section (23a).

  This innovative microtube is part of the microchannel structure (2) in the microfluidic device (1). The device, the microchannel structure, and the unit rotate around the rotation axis (3), for example, to pass the liquid separation portion adjacent to the upstream side of the valve I (24) through the valve, and further to the valve I ( 24) designed to be able to create forces, such as centrifugal force and / or hydrostatic pressure, that are transported into the part of the structure downstream and processed for processing there. For example, in non-rotating or low-speed rotating situations, and in particular the liquid separation part or its surface meniscus from a lower height to an upper height and / or a liquid inlet port (port = opening on the device surface) of the microchannel structure Part) to the first valve position, a self-sucking capillary force can be used as an aid in the transport. In addition, this unit is provided in the microfluidic device, and forces other than those described above are used for transporting liquid via the valve I and / or for transporting liquid within or between different parts of the microchannel structure. You may make it do. Such forces other than those mentioned above include the gravity of the earth.

  The inlet end (16) of the microtube I (17) is at a higher position than the outlet end (18), and in some variations, the outlet end at a higher position and the inlet end at a lower position. The case where the part may be reversed is not excluded.

  Microtube I (17) may be continuously upward or may include two or more sections that are staggered continuously upward or downward. The inlet end (16) and / or the outlet end (18) may be part of an upward section, a downward section, or a horizontal section. The term “horizontal” means that the entire section is at a constant height, and in the case of a centrifuge based system this is tangential / orthogonal to the radius through the center of the section. It means that there is an essentially constant radial distance (arc) including a straight line. When the angle length of the horizontal section exists, the arc degrees ≦ π / 20, ≦ π / 40, and ≦ π / 80. “Continuously upward” and “continuously downward” include that the section may be provided with a “horizontal” extension (= part of the section). The horizontal section is between the upper section and the lower section. Between adjacent upper and downward sections (23a, 23b), there is a horizontal section that forms an upper or lower bend ("elbow"), possibly with the upper tip (22) or the lower tip, respectively. In a preferred variant, the microtube I (24) has the shape of an upper bend, which is provided with an inlet end (16) at a height above or below the outlet end (18). , With a horizontal section at one or both of these ends.

  The capillary valve I of unit B and the other capillary valves may be of the same type as that of unit A. Reference may be made to Unit A, an overview of microfluidic devices, background art, and publications cited in these portions of the specification. In a preferred embodiment, the capillary valve I is a finger valve as defined in unit C.

  The capillary valve I (24) is located above the upper section (23a) or in the horizontal extension (if any) and / or at the same or higher position as the inlet end (16). It is preferable. The upper section (23a) is a part of an upper bent portion provided with an upper tip and an outlet end (18) at a position lower than the inlet end (16) of the microtube I (17). Also good. If the microtube I (17) includes a downward section, eg, includes an outlet I (18) at a lower height than the inlet end (16), the capillary valve I (24) is placed in the downward section. Can be positioned above or below the height of the inlet end (16).

  In addition, when the capillary valve I (24) is located in the micro tube (17), the micro tube I (17) has one or more at the inlet end (16) of the micro tube I (17). Additional capillary valves may be provided, for example a valve (25). In this regard, unit D, unit A and unit C can also be referred to.

The inlet end (16) of the microtube (17) can be connected to the upstream microcavity I (4) shown below:
a) Separation microcavity of the type described for example in unit A, unit E.

b) provided with a valve corresponding to the valve I associated with the liquid outlet, used for controlling the downstream transport of the measured separation part, for example Unit A, WO 02074438 (Gyros AB) A volumetric microcavity (4a) of the type described in.

c) Liquid holding microcavities such as mixing and / or reaction microcavities. Such liquid-retaining microcavities are, for example, International Publication No. 2003018198 (Gyros AB), International Publication No. 2005049976 (Gyros AB), PCT / SE2005 / 001887, and Gyros Patent AB, December 12, 2005. US SN 11 /? Of the title “Microfluidic Assays and Microfluidic Devices” submitted to ? ? ? ? The presence or absence of a valve between the inlet function, the microcavity, and the valve provided at the liquid outlet (related to valve I) The type that works regardless of

d) A reaction microcavity of the type described in WO 02075312. This type relates to one or more liquid inlets, each of which may or may not be associated with a valve, and a flow regulator that controls the flow of liquid through the microcavity and / or the valve within the liquid inlet. And a liquid outlet.

e) Other.

  A general holding microcavity is described, for example, in WO03018198 (Gyros AB). Flow control means include narrow and relatively long discharge microtubes, perforated beds, membranes in reaction microcavities, and others. For this, reference can be made to International Publication No. 02075312 (Gyros AB) and International Publication No. 030259898 (Gyros AB). Capillary valves are preferred, for example, for the innovative types of finger valves described herein, and the discharge function of reaction microcavities, separation microcavities, and mixing microcavities.

  Alternatively, the inlet end (16) of the microtube I (17) is a) bifurcated with two or more inlet and / or outlet ends of other microtubes intended for liquid transport It may be part of the microtube or b) directly or indirectly connected to the liquid inlet port of the microchannel structure (ie the opening on the surface of the device containing the mechanical structure containing the unit) .

  In addition, as described in units A and E, the upstream microcavity (4 in the previous paragraph, with the proviso that the microtube I (17) is part of the liquid inflow function of the microcavity II (20). ), The outlet end (18) of the microtube I (17) is a downstream microcavity II, which may be a reaction microcavity, a separation microcavity, a volume defining unit / capacitance microcavity, etc. You may connect directly to (20).

  Alternatively, the outlet end (18) of the microtube I (17) is a) a branching micro with two or more inlet and / or outlet ends of other microtubes intended for liquid transport. It may be part of the tube, or b) directly or indirectly connected to a microchannel structured liquid discharge port (ie, an opening in the surface of the device containing the mechanical structure containing the unit).

One innovative aspect of unit B is a method for transporting liquid within a microchannel structure comprising this unit and provided in a microfluidic device. This method comprises the following steps:
i) providing a microfluidic device incorporating a microchannel structure (2) with unit B; Unit B consists of an upstream microcavity (4) connected to the inlet end (16) of the microtube I (17) and 0, 1 located upstream of the capillary valve I (24) in the microtube I (17). One, two or more capillary valves, a front meniscus of the liquid fraction in the capillary valve in the microtube I (17), and an inlet end generally located above the valve I (24) ( 16) and a back surface meniscus disposed upstream.

  ii) A driving force is applied to the liquid separation portion, and the front meniscus is stopped by the capillary valve I (24), so that the front meniscus becomes the capillary tube of the micro tube I (17) upstream of the capillary valve I (24). Moving continuously over the valve. This step is subject to the condition that it is executed only if one or more capillary valves are provided upstream of the capillary valve I (24) in the microtube I (17).

iii)
a) After step (i) if there is no capillary valve in the upstream capillary valve I (24) (ie the capillary valve I is the first capillary valve in the microtube I),
b) If the one or more capillary valves are provided in the microtube I, after step (ii)
A step of moving the front meniscus over the capillary valve I (24) by applying a sufficient driving force to the separation portion when moving the front meniscus over the capillary valve.

  iv) Applying sufficient driving force to the fractionation part and transporting it to at least the capillary valve I, so that at least a part of the fractionation part hits the micropipe I (17) downstream of the capillary valve I (24). Moving the portion, and generally the portion downstream of the outlet end (18) of the microtube I (17).

  The back meniscus of step (i) is generally the same fractional meniscus as the front meniscus. The back meniscus is generally in the upstream microcavity (4) (if provided). In the most common variation, there is no capillary valve upstream of capillary valve I (24) in microtube I (17). If there are one or more such capillary valves, it is preferred that one of these is located at the inlet end (16) of the microtube I (17).

  A preferred variant is further that the microtube device (1) provided in step (1) is rotated around the axis of rotation (3), so that the centrifugal combined with the hydrostatic pressure created in the structure during rotation. The force presses the front meniscus and moves it over the capillary valve (s) in the microtube I (17), between the valves (step (ii)) and after the capillary valve I (24) (step iv) It is possible to create a driving force that enables downstream conveyance. The combination with hydrostatic pressure is important for the valve (s) arranged in the upward section (23a), for example encompassing the inlet end (16) of the microtube I (17). After passing through one valve, to reach the next capillary valve, or to carry downstream transport after passing through the last capillary valve in microtube I (17) as in step (iv) In addition, capillary forces can be used as an alternative and / or auxiliary to centrifugal forces. The latter downstream transport is such that the upward section (23a) is above the initial back meniscus or the upper liquid level in the upstream microcavity (4), eg the uppermost part (7) of the upstream microcavity (4). This is especially true if it is part of an upward bend with an upper tip (22) located above I. Refer to unit A for this.

  In a particular variant of the method embodiment, the microtube I (17) has an upward bend and a valve I (24) in the upward section (23a) of this bend. It is therefore advantageous to form a continuous liquid plug from the valve I (24) into the downward section by means of a front meniscus. This downward section is, for example, below the height of the back meniscus in the upstream microcavity (4) and / or below the upper liquid level I of the uppermost part (22) of the bend and / or the microtube It is below the height of the inlet end (16) of I (= the liquid outlet (6) of the upstream microtube (4)). The liquid plug assists in the conveyance, so that the rotation speed can be reduced after the front meniscus passes the top height / upper tip (22) of the micro tube I (17). Refer to Unit A for details.

Unit C. Capillary stop function (finger valve, finger ventilation, etc.)
This unit comprises a micro tube I (17) provided with an inlet end (16), an outlet end (18) and a capillary stop function. The microtube I (17) can be used as a liquid carrying microtube or a venting microtube depending on its design and location within the microchannel structure.

  The segment (46) of the microtube I (17) defines a capillary stop function (24) by including abrupt changes in geometric surface features. This change may include a sudden change in cross-sectional dimensions (transverse change, not shown) and / or a sharp increase in wettability on chemical surface features. This change and / or increase is generally localized on the surface of the microchannel (44a or 44b) in the sense that the split part) 46) has a specific length encompassing the entire microtube I or part thereof. It occurs in. For this reason, the end portion of the microtube I is not included at all, or one end or both ends are included in this divided portion. This is because in the case of an increase in non-wetting characteristics, at least one of the inner walls of the microtube, as described in the background art, an overview of the microfluidic device, the publications referenced in these parts of the specification. It means that two, two or more have this type of change.

  The inlet end (16) of the microtube I (17) is at a higher position than the outlet end (18), which in some variations is higher than the higher end outlet end (18). The case where the lower entry end (16) may be reversed is not excluded.

  There are two main uses for the capillary stop function of this unit: a) a vent for gas / air inflow and exhaust only, b) stop / flow of liquid conveyed through the microtube valve. Application (a) is intended for the outlet end (18) in contact with air / gas only, while the inlet end (16) of the microtube I is in contact with liquid. Application (b) intends that both ends are in continuous and / or concomitant contact with the liquid.

  Characteristically, at least one of the divided parts is divided into two or more microchannels (fingers) (42), so that the capillary stop function (24) according to the invention is a finger valve or finger vent. It is mentioned that. The inner surface area defined by the change in surface characteristics is located in the microchannel (42) or adjacent to the inlet (45) and / or outlet (43) of the microchannel (42), or these Is covered. Abrupt changes in geometric surface features include, for example, abrupt changes in the cross-sectional dimensions defined by the inlet end (45) or outlet end (43) of the microchannel (42). The inner surface area with increased non-wetting (44a) may begin and / or terminate at the inlet end (45) and / or the outlet end (43) of the microchannel (42) and / or It may be contained entirely within the microchannel and / or may cover one or both of the inlet end (45) and outlet end (43) (44b) or both of the microchannel (42). This non-wetting range may be two or more related to the same stop function, for example one sub-range at the inlet end of the microchannel and another sub-range at the outlet end. The above sub-ranges can be subdivided. The inner surface between these two sub-ranges of the microchannel is generally wettable. It is often advantageous to maintain hydrophilicity at the opposite ends adjacent to or covering only the inlet (45) or only the outlet (see below).

The split (46) defined in the innovative capillary stop function (24) above extends in:
a) Between the most upstream portion of the upstream end (45) of the microchannel (42) and the upstream end (47) of the non-wetting surface area (44a or 44b).

b) Between the most downstream portion of the downstream end (43) of the microchannel (42) and the downstream end (48) of the non-wetting surface area (44a or 44b).

  Generally, the number of microchannels (42) is 2, 3, 4, 5, 6, or more, and the upper limit is 15, 20, 30, 40 or more. . At least two of the microchannels within the capillary stop function according to the present invention are functionally equivalent in the following sense: a) If the function is purely ventilation, no liquid will pass through any of the microchannels B) If the function is a stop / flow valve, it is essentially parallel (actually the time change allowed to advance between microchannels in use is from 0 seconds up to 15 seconds) The liquid can pass through at least two, for example all, of the microchannels (in parallel). To this end, each microchannel (42) is essentially associated with one or more features selected from length, curvature, cross-sectional dimensions such as depth / width / range, longitudinal variation, etc. It must be the same shape. Thus, the finger-type capillary stop microchannel (42) is clear and well-defined in the sense that it is not a random pore with a spectrum and cross in the direction like a conventional porous plug, floor, membrane, filter. Is defined.

  The range of changed surface features is, for example, at the beginning of the inlet end (16) of the microtube I, before and after it and / or at the end of the outlet end (18), before and after it. (17) can be partially or completely coated.

  The length, depth, width of the microchannel (42) is the stop function, in particular a valve or vent, the size and shape of the cross-sectional dimensions of the microtube before and / or after the microchannel, the cross-sectional dimensions of the respective microchannel Depending on the desired flow rate before or after the microchannel, the desired driving force including the rotational speed of the centrifuge-based device, the position on the device, the manufacturing technique, etc.

The length of each microchannel (42) may be different or equal for two or more, eg, all. Typical lengths of microchannels are ≧ 0.1, for example ≧ 0.5, ≧ 0.75, ≧ 1, ≧ 3, ≧ 5, ≧ 10 and / or microchannels The width and depth of the longest are ≦ 10 ² times, ≦ 10 ³ times, ≦ 10 ⁴ times, and ≦ 10 ⁵ times. If the width and depth change along the length of the microchannel, the longest width and depth are compared. In absolute values, typical lengths are within an interval of ≧ 5 μm, for example ≧ 10 μm, ≧ 50 μm, ≧ 100 μm, ≧ 500 μm, ≧ 1000 μm, ≧ 3000 μm, and / or ≦ 50000 μm, for example ≦ 25000 μm, ≦ It may be 10,000 μm, ≦ 5000 μm, ≦ 1000 μm.

  The depth and / or width may be different or equal for two or more, eg, all microchannels (42). In absolute values, typical depths and / or widths are ≧ 1 μm, for example ≧ 5 μm, ≧ 10 μm, ≧ 20 μm, ≧ 50 μm and / or ≦ 500 μm, for example ≦ 200 μm, ≦ 100 μm ≦ 50 μm or ≦ 20 μm.

If the microchannel (42) is shorter than the microtube I, the sum of the open cross-sectional area (Asum) of the microchannel (42) at the upstream end (45) and / or the downstream end (43) is divided. It is equal to or larger or smaller than the open cross-sectional area (A _before , A _after ) of the microtube (42) immediately before and / or immediately after the portion. In general, the ratio of A _sum / A _before (and / or A _sum / A _after ) is within an interval of ≧ 1, for example ≧ 2, ≧ 5, ≧ 10 and / or within an interval of ≦ 1 For example, it may be ≦ 0.5, ≦ 0.2, or ≦ 0.1. If the depth and / or width are different at a particular position, this spacing refers to the maximum depth and width at that position. Compare with trapezoidal or triangular cross section.

  In a variation of the unit C valve, the inlet end (16) and / or outlet end (18) of the microtube I (17) is one of the branches as described in units A, B, E. Or connected to a microcavity. Alternatively, the inlet end (16) may be connected directly or indirectly to the inlet and outlet ends of the same microtube similar to the outlet port. In principle, any combination of functions as referred to elsewhere in this specification may be associated with a microtube I equipped with a finger valve according to the invention after appropriate adaptation.

  In a variant of the vent of unit C (not shown), the inlet end of the microtube I is directly coupled to a microcavity that contains the liquid or a microtube that is used to transport the liquid. This allows the outlet end of the microtube I, possibly via one or more air / gas microtubes, and / or other parts of the same microchannel structure or other on the same microfluidic device Part of the microchannel structure allows direct or indirect communication with the surrounding air. This other part is also considered as a microcavity / microtube for air / gas. The innovative finger venting function is preferably located at the inlet end of the microtube I, or alternatively the microtube I is provided with an additional capillary stop function located in the above position. This additional capillary stop function may or may not be a finger vent.

  The microtube I (17) may be located downstream or upstream of the finger function (24), which has a section with a larger or smaller cross-sectional area than on the opposite side of the function. In addition, it is preferable that the cross-sectional area is smaller in the downstream than in the upstream of the finger function. This is especially true when the finger function is a finger valve. This can be compared with Unit A.

  Microtube I (17) may include one or more additional capillary valves. One of these additional valves (25) is preferably located upstream of the finger valve (24), as described for other innovative units herein (especially unit D), It is preferably located at the inlet end (16). One of these additional valves may be a finger valve or capillary valve of the type described in the background art, an overview of microfluidic devices, publications referenced elsewhere in this specification. Good.

Interesting finger valves can be achieved if the innovative finger valves are:
a) It is arranged at the outlet end (16) of the microtube I (17), typically extending from the inlet end (16) of the microtube I to the outlet end (18) (section ( 46) = Case of micro tube (17)).

b) The non-wetting range (43a) is adjacent to or covers the upstream end (47) of the microchannel (42), but at the downstream end (48) of the same microchannel. Adjacent, uncovered, and the downstream end of the microchannel is in fluid communication with means that can selectively wet the microchannel interior from this end of the microtube I / microchannel. If so.

  In a particularly preferred variant of (a), the valve I (= section) and the microtube I coincide, and the inlet end of the valve I / microtube I is directly attached to the upstream microcavity, The outlet end of the microtube I is directly attached to the downstream microcavity. Both of these microcavities can be selected as outlined for the upstream microcavity (4) and downstream microcavity (20) of unit A. This can be referred to above.

  In variant (b) above, the term “means for selectively wetting” includes: a) a downstream microcavity having a wetting inlet in fluid communication with the outlet end of microtube I; and b) micro Including the outlet end of tube I being part of a bifurcated portion with the end of the microtube that can be separately provided to the downstream end of the microchannel. When providing liquid via this type of wetting means, the liquid is aspirated to non-wetting portions within the hydrophilic microchannel. For this type of valve, an increase in liquid pressure allows liquid to break through the valve downstream, and in addition to the reaction microcavity, the mixing chamber, and the holding microcavity that holds the liquid under other pressures. It is expected that it can be adapted for use in the outlet end. See the microfluidic device outline for various microcavities.

  The micro tube I (17) of the unit C may be provided with one or more upper sections (23a) described in the section B, and a finger valve (24) is incorporated in at least one of these upper sections. It is preferable. The upper section (23a) may be a part of the upper bent portion as described in other parts of the present specification. The micro tube I may have other shapes as described in the units A to B.

One aspect of the present invention associated with unit C is a method utilizing a microfluidic device incorporating a microchannel structure with this unit. This method is a method of transporting the liquid through the capillary stop function of the unit C. This method comprises the following steps:
i) providing a microfluidic device incorporating a microchannel structure; This microchannel structure comprises a unit C, which, as defined above, is a front meniscus of liquid separation at the upstream position of the capillary stop function (24), upstream of the inlet end (16), and capillary A back meniscus located above the height of the stop function (24) is provided.

ii) Applying driving force to move the front meniscus as follows:
a) If the function is a valve, perhaps the first step is to stop the front meniscus in the stop function and then restart the movement to move to and over the capillary stop function.

      b) If the function is a vent, move to this function.

  In step (i), the back meniscus is the same fractional meniscus as the front meniscus. Also, generally, the back meniscus resides in the upstream microcavity (4) (if provided).

  The driving force in steps (i) and (ii) may be air / gas overpressure or hydrostatic pressure applied to the back surface meniscus of the separation portion, centrifugal force, or the like. Capillary force can also be used for transport / movement to the capillary stop function (24). To pass through the capillary stop function (24), it is necessary to actively increase the driving force, and in this case, the driving force can be selected from the same multiple forces as in the initial movement, excluding the unsuitable capillary force. Means. If the device is designed to utilize centrifugal force, it is preferable to increase the rotation. After step (ii), the fractionation part or part of it can be moved further into the downstream microchannel structure using a driving force or combination of forces other than step (ii). Centrifugal force can be substituted and / or assisted, for example, with capillary force and / or hydrostatic pressure. If the finger valve is coupled to or part of any of the units A to F, steps (i), (ii) are adapted to the requirements of the relevant method steps.

Unit D Protected Capillary Valve Unit This unit comprises a liquid carrying microtube (17) provided with an inlet end (16) and an outlet end (18) and a capillary valve I (24).

  It is a feature that the microtube comprises one or more additional capillary valves (25). The capillary valve I (24) is typically a finger valve as defined in unit C, and preferably one or more additional valves are arranged upstream of the valve I. Also, the additional capillary valve is a finger valve or described in relation to other units in other parts of this specification, background art, overview of microfluidic devices, and publications referenced in these parts. It may be a type of valve. One of the additional valves (25) is preferably arranged at the inlet end (16) of the microtube I (17). In this case, there is a condition that the valve I (24) is then placed in the micro tube.

  The innovative microtube I (17) is part of the microchannel structure provided in the same type of microfluidic device as described in units A to C, E to F.

  The inlet end (16) of the microtube I (17) is typically located above the outlet end (18), where in some variations the outlet end is at a higher position. It is not excluded that the inlet end (16) in the lower position with the part (18) may be reversed.

  As described in units B and C, the microtube I (17) has one or more upper sections (23a) and / or one or more lower sections (23b) and / or one or more horizontal sections. One or more upward bends, one or more downward bends, an upper tip (one or more) (22), etc. may be included. Inside these parts, most commonly in the upper or lower section of the upper bend, a capillary valve I, for example in the form of a finger valve, may be provided with considerable care for each particular case desired function. . Refer to units B and C for details.

  In unit D, the inlet end (16) or outlet end (18) of the microtube (17) is part of a branch, as described in units A, B, C, E, Or connected to a microcavity. The inlet end (16) of the microtube I may be connected directly or indirectly to the inlet and outlet ends (18), the outlet port. In principle, any appropriate combination of the functions referred to may be associated with the microtube I of unit D if appropriate adaptations are made.

One aspect of the unit D according to the invention is a method for transporting a liquid in a microchannel structure with the unit D. This method can also be applied to units B and C if they have two or more capillary valves as described above. This method comprises the following steps:
i) providing a microfluidic part comprising a microchannel structure comprising unit D;
ii) providing a liquid fraction (= valve 1, front meniscus in valve 1) adjacent to the uppermost stream of the capillary valve;
iii) A fractionation part over valve 1 by stopping the meniscus at the next capillary valve (valve 2) by increasing the driving force and possibly reducing the driving force after the meniscus has passed through valve 1 Or moving part of it (frontal meniscus);
iv) Stop the meniscus at the next capillary valve (valve 3) (if provided) by increasing the driving force and possibly reducing the driving force after the meniscus has passed through the valve 2 Moving the meniscus over valve 2 by:
v) repeating steps (iii) and (iv) until the meniscus passes through all capillary valves of microtube I;
vi) moving the meniscus through the outlet end of the microtube I;

  In this method, the back meniscus is arranged as described for the method aspects of the units B and C.

  Due to the hydrophilic nature of the microtube (self-suction type), the driving force is reduced after the meniscus has passed through each capillary valve. That is, it can depend in part or in whole on the capillary transport (passage) between the valves.

  In a preferred variant, the device is adapted to use the centrifugal force obtained by its rotation. Increasing the driving force means an increase in rotation. In a variation in which unit D described herein is incorporated into any other unit, the method described above can be adapted to the method of these units.

  As described in the other units section of this specification, the microtube I (17) has a maximum of two capillary valves (25, 24), of which the most upstream (25 ) Is a capillary non-finger valve, preferably located at the inlet end (16), and the next valve (24) is preferably a capillary finger valve.

  In a preferred variant, the inlet end (16) of the microtube I (17) defines an intersection between the microtube I and the transport path, which reduces the efficiency of the capillary valve. Liquid containing potential material and located downstream of the first capillary valve is transported and allowed to flow downstream into the path by bypassing the inlet end of the microtube. These downstream portions do not coincide with the downstream portions of the path branching into the microtube I. For this, reference can be made to the description of the modifications of the units A to E. In these descriptions, the provided upstream microcavity (4) probably has a lower part (4b), which may harm the capillary valve, for example by clogging or absorption. Related to the downstream part of the transport path for transporting material. Typical of the harmful materials are described in the problem-solving part according to the invention and in the part of the specific unit.

Unit E A unit that separates the upper phase, typically the liquid phase, from the phase that typically contains particulate material. This unit comprises:
d) A separation microcavity (4) provided with a liquid inlet I (5) and a liquid outlet I (6). The liquid inlet I (5) is higher than the liquid outlet I (6).

e) Liquid transport microtube I (17) having an inlet end (16) directly connected to the liquid outlet I (6) and an outlet end (18) at a lower position than this (and the liquid outlet I). .

  The separation microcavity is associated with the upstream microcavity in unit A. The liquid outlet I (6) is located in the middle between the height of the lowermost part (8) and the height of the top (7) (uppermost part) of the separation microcavity (4), and the microcavity (4) A lower part (4b) and an upper part (4a).

  The separation microcavity (4) can hold a predetermined liquid volume, thereby defining an upper liquid level I therein. This upper liquid level is equal to or lower than the height of the uppermost part (7) of the microcavity and higher than the height of the liquid outlet I (6).

  A microfluidic device including a microchannel structure, which is a part of this unit, rotates around a rotation axis to separate a liquid containing a high-density material and a lightweight material into an upper phase and a lower phase. It is designed to discharge this upper phase to the lower part of the microchannel structure via outlet I (6) and microtube I (17). Discharge to the downstream portion utilizes centrifugal force created by rotation and / or hydrostatic pressure accumulated in the microchannel structure during rotation and / or capillary force. Other forces, such as dynamic power, can be used in combination with one or more of the forces just listed. In this regard, reference can also be made to “Outline of Microfluidic Device”.

  The characteristic characteristics of this unit are as follows.

  a) Microtube I (17) is associated with valve I (24), preferably capillary valve I.

b) The direction of flow through the liquid outlet I (6) is upward. And / or
c) The liquid outlet I (6) is arranged in a downwardly bent portion of the inner wall of the separation microcavity (4). And / or d) the portion of the microtube adjacent to the inlet end (16) of the microtube I (17) faces upwards.

  The valve I (24) can be placed in or at the inflow or outlet end (16 or 18) of the microtube I, and at present, in most variants, a finger valve of the type described in unit C is preferred. It is seen. In many variants, the cross-sectional dimension of the microtube I is larger upstream than downstream in the case of valve I, with a factor ≧ 1, for example ≧ 2, ≧ 5, ≧ 10. This is especially true when valve I is a finger valve and / or a liquid driven height / plug product is formed in the microtube in use. For this, reference can be made to units A to C.

  The microtube I (17) typically has an upper tip (22) which is preferably located either at the inlet end (16) (liquid outlet I (6)) or inside the microtube ( Upper tip = upward elbow). This upper tip (22) may be at the same height as the liquid outlet I (6) of the separation microcavity (4), in which case in a preferred variant the microtube I is provided with a first short horizontal section, Next, a downward section heading downward is provided at the outlet end (18). Alternatively, the upper tip (22) may be located above the liquid outlet I (6), for example above the upper liquid level I of the separation microcavity (4) and even the top of the separation microcavity (4) ( It may be above 7). In these latter variants, the upper tip (22) starts from the upward section (23a) and continues to the downward section (23b) where the joint between the sections defines the upper tip (22). It is contained in the modification of pipe | tube I (17). In this type of upper tip, a horizontal section may be provided between the upward section and the downward section. In the variant described in this paragraph, the valve I (24) has an upper tip (22) and possibly upstream of it (ie in the upstream section (23a)) and above and below the upper liquid level I, for example, It is arranged at a position of 25% or more of the height between the inlet end (16) and the upper tip (22). The preferred relative position of the valve in the upstream section (23a) is even higher, for example about 50% or more or 75% or more of the height between the inlet end (16) and the upper tip (22). preferable.

  In one of the most preferred embodiments, the valve I (24) is located in the upward section (23a) below the level of the upper liquid level I and the upper tip (22). By filling the microcavity (4) with a predetermined liquid volume, the back meniscus is placed at the upper liquid level I and the front meniscus is the first valve in the microtube (17) (this is for example described herein) If there is no other valve as described, it is placed in valve I (24)). Subsequent rotation of the device balances the back meniscus and the front meniscus at the same height above valve I (24). When the rotational capillary force is slowed, the front meniscus moves to the upper tip (22), and then when the high speed is resumed, the contents of the upper part (4a) of the separation microcavity (4) are transferred to the liquid outlet I (6 ) Is quickly discharged to a height of In the unit A, when the front meniscus moves downward and a continuous liquid plug is maintained, the rotational speed can be reduced while the upper portion is emptied. This includes that it is preferable that the size, shape, internal volume, etc. of the separation microcavity (4) and microtube I (17) are accurately matched to each other. In this regard, reference can also be made to the description of units A to C and the related method aspects in which other relative positions are listed.

  Valve I (24) may also be located downstream of the upper tip.

  In addition, the micro tube I (17) is a valve of the valve I (24), particularly when the valve I (24) is a capillary finger valve, or a valve that is easily clogged or susceptible to damage by the liquid used. An additional valve (25) arranged upstream may be included. This additional valve is preferably located at the inlet end (16) of the microtube I (17) and is selected as a valve that is less susceptible to damage by the liquid used. This variation is also effective when the microtube I (17) includes a downward bend or other shape that facilitates collection of particulate material and liquid at a location upstream of the valve I (24). .

  Units A to D can be referred to for the different shape of the micro tube I and the position of the valve inside the micro tube I.

  Capillary valves within the unit, such as valve I (24), are generally based on chemical and / or geometric internal feature changes in the unit's hydrophobic flow path according to principles well known in the art. This change may be a rapid increase in the cross-sectional dimension of the microtube (transverse change) and / or a rapid increase in non-wetting of the inner surface of the microtube, in which case the change will flow Happens in the direction of This change is also generally local (fracture), for example, non-wetting / hydrophobic surface breakage in a hydrophilic flow path. The non-wetting inner surface can roughen the surface and / or expose fluorinated hydrocarbon groups. In this regard, reference may also be made to the background art, an overview of microfluidic devices and the publications referenced under these titles.

  The liquid flow that has started to be discharged from the liquid outlet I (6) is directed in various directions in relation to the centrifugal force at the liquid outlet I (6). This flow direction may be (a) with an upward / inward component (inward radius component) or (b) essentially tangential (horizontal). Thus, the direction of flow relative to the direction of the centrifugal force at the liquid outlet I (6) is at least partly opposed to the centrifugal force in the alternative form (a) and essentially orthogonal to the centrifugal force in the alternative form (b). It may be a direction. This is expressed as the angle (α) relative to the direction of the centrifugal force at the liquid outlet I, and in the alternative form (a) 90 ° ≦ α ≦ 270 °, for example 95 ° ≦ α ≦ 265 ° ( Counter), and in alternative form (b) it may be 90 ° ≦ α ≦ 100 °, for example 90 ° ≦ α ≦ 95 ° and / or 260, such as 265 ° ≦ α ≦ 270 °. It may be ° ≦ α ≦ 270 ° (orthogonal).

  The angle (α ′) between the centrifugal force at the liquid outlet I (6) and the inner wall around the liquid outlet I (6) is, for example, −90 ° ≦ α ′ ≦ −5 and / or in the alternative (a) −90 ° ≦ α ′ ≦ 0 ° and / or 0 ° ≦ α ′ ≦ 90 °, such as 5 ° ≦ α ′ ≦ 90 °, and in alternative form (b), for example −5 ° ≦ α It may be −10 ° ≦ α ′ ≦ 10 °, such as “≦ 5 °, or in particular α ′ = 0 °. The direction of the inner wall and / or the direction of the associated opening in alternative form (b) essentially corresponds to the direction of the centrifugal force.

  The portion of the microtube I (17) adjacent to the liquid outlet I (6) of the separation microcavity (4) has a direction that opposes a direction selected from among the main flow directions in the liquid outlet. Although preferred, these two flows need not be in the same direction.

  As explained in unit A above, the liquid outlet I (6) separates the separation microcavity (4) into a lower part (4b) and an upper part (4a). In a typical case, the lower part (4b) constitutes ≧ 10% of the total volume of the separation microcavity (4), for example ≧ 25%, ≧ 50%, ≧ 70%, ≧ 80%. The exact relative volume of these parts is determined by the relative volume of the phase obtained after these parts are formed by device rotation. In many cases it is important that the lower part (4b) should have at least the same phase as the lower phase. Therefore, the lower surface of the phase discharged from the liquid outlet I (6) must be lower than this outlet by maintaining the liquid level between this lower surface and the liquid outlet I (6). ≧ 10 μm, ≧ 50 μm, ≧ 100 μm, ≧ 200 μm.

  The separation microcavity (4) may taper towards the height of the inlet (5) and / or outlet (6) or towards this inlet and outlet itself. Tapering is an acute angle with at least one, two or more inner walls at the outlet / inlet of the object, along with the direction of main flow through the taper, or with a straight line (radius) from the axis of rotation to the outlet of the object. (Β <90 °) is formed. This angle (β) is preferably in the interval of 10-60 °, more preferably in the interval of 20-40 °, such as 25-35 °, and preferably about 30 ° is selected. These intervals can also be applied to pure ventilation outlets. Tapering, in conjunction with the liquid outlet and the pure vent outlet, prevents the formation of bubbles during the filling of the microcavity with liquid.

  The separation microcavity (4) may be constricted at the height of the liquid outlet (6). This stenosis can be defined by the tapering described in the previous paragraph.

  Stenosis and / or taper means that the maximum cross-sectional area of the microcavity, or the upper and / or lower part thereof, is greater than the cross-sectional area at the height of the outlet / inlet of interest by a factor> 1, for example ≧ 1.25, ≧ 1.5, ≧ 3.0, ≧ 5.0 means large.

  In a preferred design, the cross-sectional area in the upstream microcavity is larger, for example with a factor ≧ 1, such as ≧ 2, ≧ 5, ≧ 10, upstream of the liquid outlet I (6) than in the microtube I (17).

  Taper and stenosis are described in more detail in Unit A.

  The lower part (4b) of the separation microcavity (4) communicates with one or more outlets (14) that open into the surrounding air only to evacuate the air pushed out by the liquid entering this part. ing. The actual discharge opening (14) (vent vent port) of this type provided on the surface of the device is preferably arranged above the liquid inlet I (5) and further to the discharge opening. It is located above the actual inflow opening (9) (liquid flow inflow port) provided on the surface of the device for the introduction of liquid first. In connection with the outlet (s) of the above type, if the associated vent outlet opening (14) provided on the device surface is lower than the liquid inlet (4) of the upstream microcavity (4). A capillary stop function (15a) (downstream end) can be provided. This allows the separation microcavity (4) to form a U-shaped or downward bent microcavity. If there are a plurality of venting openings (14) in the downstream part (4b) of the microcavity, this part (4b) can be divided into two or more fingers (finger microcavity).

  If, for example, an overflow opening (10) is provided at the height of the liquid inlet I (5), the upper part (4b) of the upstream microcavity (4) can be used as a capacitance measuring microcavity. The following can be referred to for this. This measurement appears to be more accurate when the capillary stop function (15a) associated with the venting function (14) of the type described is provided below the liquid outlet I (5). The capillary stop function (15a) is preferably the finger vent described in unit C. For further explanation on this, reference can be made to unit A.

  The lower part (4b) has a liquid outlet I 'for discharging material from the lower part after the upper part has been emptied via the liquid outlet I (not shown). In this case, the liquid outlet I 'is below the liquid outlet I.

  The upper part (4b) of the separation microcavity (4) may be part of a volume defining unit. This capacity defining unit is of the type outlined in, for example, the upstream and downstream microcavities of unit A or described in WO 02074438, WO03018198 (both are gyros AB) It may be. This simply means that the liquid inlet I (5) is connected to an inflow microtube I (8a) with an overflow opening (10) at the same height. The overflow opening (10) is connected to a downwardly facing overflow microtube (11), and this overflow microtube (11) appropriately rotates the device by adding excess liquid added from the inflow microtube. Can be selectively discarded.

  The upper part (4b) may also contain one or more additional liquid inlets, indicated by unit A.

  The outlet end (18) of the microtube I (17) can be connected directly to a downstream microcavity (20) of the type and function indicated by unit A.

  The relative dimensions of the microtube I (17) and the separation microcavity (4), including the liquid inlet, outlet, vent, valve, etc., and their locations, as outlined in unit A, Can preferably be adapted to create a drive plug height.

  The embodiment according to the invention of unit E further comprises a microfluidic method, which separates a fraction of a liquid containing a higher density and lower density material into a lower density upper phase and a higher density lower phase. And then, during the separation, at least a portion of the upper transport is transported to the downstream portion of the same microchannel structure. This method is in principle a variation of the method described in unit A, with sufficient rotation, without contamination of the microtube I with a material that, after separation, will in principle only be seen in the lower phase. The liquid in the upstream microcavity can be centrifugally fractionated into a high density lower phase and a low density upper phase. This method aspect of unit D further comprises further processing the upper fraction transported downstream, eg by mixing for dilution, mixing with a reactant containing another fraction, an enzyme assay protocol, affinity Performing a biological reaction included in an assay protocol such as an assay protocol. These assay protocols may involve heterozygous assay protocols, homogeneous non-competitive assay protocols such as sandwich assays, heterogeneous competitive assay protocols, and related homogenous reactions and assay protocols. By performing these assay protocols, characterization of uncharacterized entities in the sample can be performed, for example, quantitative or qualitative determination of the total amount of analyte.

F. Detection unit Unit F is part of a microchannel structure with a built-in detection microcavity (49). An inflow micro tube (transport micro tube) for transporting the liquid (35) to the detection micro cavity (49) is attached in the upstream direction of the detection micro cavity. The detection microcavity is used to detect reaction results that occur in the detection microcavity upstream of the detection microcavity (49) or in the reaction microcavity (20). Centrifugal force is used to transport liquid between and through the microcavities. In this feature, the detection microcavity (49) comprises a detection microtube, which has an inlet portion (36), an outlet portion (32), and an upward or downward meandering portion (39) between them. Provided.

FIG. 4 shows a meandering microtube (39). The serpentine microtube has a plurality of continuous returns (r ₁ , r ₂ , r ₃ , r ₄ , r ₅ , r ₆ , r ₇ , r ₈ ...) and is adjacent along the serpentine portion Between two consecutive returns (r ₁ , r ₂ ; r ₂ , r ₃ ; r ₃ , r ₄ ; r ₄ , r ₅ ...), an intermediate interval (r _1-2 , r _2-3 , r _{3 -4} , r _4-5 , r _5-6 , r _6-7 , r _7-8 ). The vertical position of the return and the intermediate section increases in the vertical direction of the meandering part (mainstream direction of the meandering part), while the horizontal position of the return is alternately arranged around the center of the latitudinal direction. It is common to all or a part of the meandering portion having more continuous returns. Flow direction (= direction of section) in every second intermediate section (r _1-2 , r _3-4 , r _5-6 , r _7-8 ,... Or r _2-3 , r _4-5 , R _6-7 , r _8-9 ...) are either left or right, while each pair of two consecutive intermediate intervals (r _1-2 , r _2-3 ; r _{2 -3} , r _3-4 ; r _3-4 , r _4-5 ; ...), the flow direction in the first section is the left direction or the right direction, and the flow direction in the second section is This is the opposite (alternating horizontal direction of the intermediate section). The right and left are for the main direction of the meandering part.

  In a centrifugal force-based system, downward and upward meander means that the main direction of flow through the meander includes a component toward or along the centrifugal force, respectively. In other words, the first return is higher than the final return of the downward meander, and vice versa for the upward meander. In a preferred case, the downward and upward meanders may be vertical, meaning that the main direction (longitudinal direction) of the meander coincides with the direction of the centrifugal force. Reference can be made to FIG. 4 illustrating an upward vertical meander.

  On the priority date, a typical meandering part forms an angle γ with an interval of 145 ° ≦ γ ≦ 225 ° in the case of upward meandering with centrifugal force, and −45 ° ≦ in the case of downward meandering A main flow direction forming an angle γ having an interval of γ ≦ 45 ° is provided. In relation to the vertical upward meandering portion and the vertical downward meandering portion (γ is 180 ° and 0 °, respectively), the upward meandering portion is mainly preferable, because the upward meandering portion easily manufactures a small microchannel structure. It is. In this regard, FIG. 2 and FIG. 4 can be compared.

  In a preferred variant, the meander has two, three, four, five or more returns. The upper limit of the return may vary, but is typically ≦ 50, for example ≦ 25 or ≦ 10.

  In a typical variant of the innovative meander, each intermediate section includes an extension, which is parallel to the corresponding extension of another section. In a preferred modification, this parallel relationship occurs every two intervals, and it is absolutely preferable that a parallel relationship occurs in each interval as shown in FIG.

The meandering portion of the upward direction, the continuous return _{(r 1, r 2, r} 3, r 4, r 5, r 6, r 7, r 8 ...) 2 one each return of _{(r 1, r} 3, r ₅ , r ₇ ,... or r ₂ , r ₄ , r ₆ , r ₈ ...), for example, each successive return (r ₁ , r ₂ , r ₃ , r ₄ , r ₅ , r ₆ , r ₇ , r ₈ ...) Height position (= vertical position) increases according to the flow direction. In the meandering part in the downward direction, the height position decreases according to the flow direction of the corresponding combination of returns. In the simplest of these, the increase / decrease along the meander is an arbitrary pair of consecutive returns (r ₁ , r ₂ ; r ₂ , r ₃ ; r ₃ , r ₄ ; r ₄ , r ₅ ...) between the first return and the second return, or any triple of consecutive returns (r ₁ , r ₂ , r ₃ ; r ₂ , r ₃ , r ₄ ; r ₃ , r ₄ , r ₅ ...) is constant between the first return and the third return.

  The detection microcavity (49) may be two or more serpentine portions (not shown) of two or more series-coupled identical or different shapes. Thus, the detection microtube may comprise three, four or more meanders, in which case the downstream end of the upstream meander of these meanders is the upstream end of the nearest downstream meander And is in fluid communication. This liquid communication is via a coupled microtube section. The longitudinal directions of two adjacent meandering portions may be different, for example, one is downward and the other is upward, or vice versa. For this type of detection microcavity, one, two or more, or all additional meanders are typically downward or upward.

  The detection microcavity (49) is or can be associated with a sensor (not shown) that can detect a signal representative of the reaction result. This sensor may be based on spectroscopic methods such as fluorescence or chemiluminescence (including biochemiluminescence, calorimetry, turbidimetry, absorbance, etc.), calorimetry, conductivity measurement, etc. Good. In general, the sensing principle utilized is compatible with the material between the inner wall of the detection microtube and the outer surface of the device in the detection microcavity. This can be obtained, for example, by configuring the detector (sensor) associated with the detection microcavity with a transparent or translucent material in order to detect the signal. Thus, this material may be transparent or translucent for heat and / or radiation in the UV, IR, and / or visible range. In many cases, the material may be a plastic material.

  Perform precise processing upstream of the detection microcavity (49) and between the detection microcavity (49) and the reaction microcavity (20), for example, where the reaction is monitored by measurements in the detection microcavity. And / or various functions may be provided for transporting the liquid prior to entering the detection microcavity. Thus, a) a routing function that prevents liquid fractions that could harm the detection microcavity from passing through the detection microcavity, b) a reaction chamber with a reagent that neutralizes interfering substances from the liquid, b It may be a stop / flow valve, c) a flow restriction function that prevents the flow of liquid through the reaction microcavity. These various functions are well known in the art and are also described or referenced herein. The main function of the stop / flow valve in the innovative unit and the flow regulation function are other including proper reaction between reactants and / or transport between the upstream part of the microchannel structure and the detection microcavity In order to stabilize the appropriate response between treatments. A preferred valve is a non-closed valve such as a capillary valve. Flow control functions include perforated beds, membranes, etc. disposed within the reaction microcavity. In addition, narrow and / or long microtubes downstream of the reaction microcavity also serve as sufficient flow regulation. The inner surface of the flow restricting function can function as a solid phase for one or more immobilized reactants used within the desired reactant (s) in a manner similar to a porous bed. This desired reactant includes, for example, a regulated microtube or the inner surface of a porous bed, a membrane, a plug, and the like. The solid phase of the type referred to above is preferably part of the reaction microcavity (20).

  Non-closed valves such as capillary valves are described under the background art, an overview of microfluidic devices, and publications referenced in these portions of the specification. In particular, International Publication No. 02075312 (Gyros AB) and International Publication No. 030259898 (Gyros AB) list various flow regulating means or functions.

  The microcavity (20) upstream of the detection microcavity may have various geometric shapes. The cross-sectional dimension may not change, or a non-branching type micro tube provided with an enlarged portion (micro cavity) may be used. This may be a mixing microcavity, a reaction microcavity, etc., or one for mixing two or more liquid fractions of the same or different volumes in the microcavity, including dilution, Two or more liquid inlets may be included. At least one fractionation portion contains one or more reactants used for the reaction (s) occurring within the reaction / detection microcavity (20/49). Upstream, each liquid inlet of the microcavity (20) is directly connected to the liquid inlet array with a volume defining unit with an inlet port, possibly interposing a volume defining unit for one or more microtubes in the inlet array. Or indirectly. For example, International Publication No. 02074438 (Gyros AB) and International Publication No. 03018198 (Gyros AB) can be referred to.

  Unit F is found in the microchannel structure of the microfluidic device and rotates around the axis of rotation to create centrifugal force. This centrifugal force assists in moving the liquid from the upstream portion of the microchannel structure through the detection cavity. This transport is mainly caused by the centrifugal force created by the rotation and / or the hydrostatic pressure accumulated in the microchannel structure during the rotation and / or the capillary force (self-suction). For this, the outline of the microfluidic device can be referred to.

The part according to the invention of the unit F can further comprise reactions occurring in the detection microcavity (49) and / or in the reaction microcavity (20) upstream of the detection microcavity in the same microchannel structure (2). The method of detecting in the solution is provided. This method
a) providing a microfluidic device with a microchannel structure equipped with unit F;
b) further comprising the step of transporting the liquid I required for detection into the detection microcavity, which includes rotation of the device to create a centrifugal force used for transport;
c) further comprising detecting the result in a detection microcavity.

  In a preferred variant, the reaction is part of the processing protocol and the serpentine portion of the detection microcavity contains liquid II prior to step (iii). In step (iii), liquid I is exchanged for liquid II, but generally they do not mix with each other.

Overview of microfluidic device A microfluidic device is a device with one, two or more microchannel structures in which, for example, analytes, reagents, products, samples, buffers and / or Treatment of one or more liquid fractions in the μl range, typically in the nanoliter (nl) range, containing various reactants, including others. Each microchannel structure has all the functions necessary to perform an experiment to be performed in a microfluidic device. The volume of the liquid fraction in the μl range is ≦ 1000 μl, for example ≦ 100 μl or ≦ 10 μl, including the nl range with an upper end of 5000 nl. This upper end is often associated with a capacity of ≦ 1000 nl, for example ≦ 500 nl, ≦ 100 nl. The nl range includes the picoliter (pl) range. The microchannel structure comprises one or more cavities and / or cavities having a cross-sectional dimension of ≦ 10 ³ μm, preferably ≦ 5 × 10 ² μm, for example ≦ 10 ² μm.

Thus, the microchannel structure may comprise one, two, three or more functional parts selected from:
a) an inlet arrangement comprising, for example, one or more inlet ports / inlet openings, possibly with volumetric microcavities;
b) Micro tube for liquid transport,
c) Reaction microcavity / unit,
d) a mixing unit comprising, for example, a microcavity as described elsewhere herein.
e) a microcavity unit for separating particulate matter from a liquid;
f) a unit that separates the dissolved, dispersed / suspended components in the sample from each other, eg by capillary electrophoresis, chromatography, etc.
g) Detection microcavity / unit,
h) Waste conduit / microcavity / unit,
i) valves,
j) Ventilation part opened in the surrounding air,
k) Anti-wicking function l) Liquid induction function, etc.

A functional part can provide two or more functionalities such as:
1. The reaction microcavity and detection microcavity coincide.

    2. The volume measurement function may comprise one or more valve functions, a measurement microcavity, and / or an anti-wicking function.

    3. The reaction microcavity may have one or more valve functions and / or anti-wicking functions.

    4). The passive valve function (capillary valve) based on non-wetting surface destruction may have an anti-wicking function or the like.

  Microcavities, such as the upstream and downstream microcavities described herein, are reaction microcavities, separation microcavities, volumetric microcavities, mixing microcavities, and flow micros, eg, associated with flow restriction means that control flow. Cavities or other retained liquid microcavities having a capacity selected from the above-listed intervals. Larger volumes for liquid samples containing analytes, diluents, and washings prior to concentration in the microchannel structure, eg ≧ 5 μl, ≧ 1 μl, such as ≧ 10 μl, but for example ≦ ≦ 1000 μl is conceivable, such as 100 μl, ≦ 50 μl, ≦ 25 μl. Therefore, larger capacity microcavities that meet these ranges are located in the upstream portion of the microchannel structure and are generally volumetric microcavities, separation microcavities that remove (separate) particulates from samples containing analytes, The sample containing the analyte is diluted with a diluent, mixed with a reagent, mixed microcavity, diluted liquid storage and / or measurement microcavity, washed liquid storage and / or measurement microcavity, and the like. Microcavities aimed at holding reagents or sample fractions containing reagents are generally small in volume and are in the range ≦ 5 μl, ≦ 1 μl, 0.5 μl, 0.1 μl, ie nl.

  The microcavity described in the innovative unit part, background art, this part of the specification, WO03018198 (Gyros AB) (holding microcavity), etc., in principle, is a microtube I (17 ) In the microchannel structure / unit of an innovative microfluidic device in direct or indirect fluid communication with the inlet end (16) or outlet end (18).

  In the following applications, Gyros AB / Amersham Pharmacia Biotech AB describes various functional units in a microfluidic device: WO9955827, WO9958245, WO No. 0207438, International Publication No. 0275312, International Publication No. 03018198, International Publication No. 0302598, and the like. Further, in the following applications, similar functional units are described by Tecan / Gamera Bioscience: International Publication No. 0187487, International Publication No. 0187486, International Publication No. 0079285, International Publication No. 0078455. International Publication No. 0069560, International Publication No. 9807019, International Publication No. 9853311.

  The inlet array includes an inlet port and at least one volumetric microcavity. One separate inlet array may be provided per microchannel structure. It is also possible to provide an inlet arrangement common to all or a subset of the microchannel structures of the device. This latter arrangement comprises a common inlet port and distribution manifold, which provides one volumetric microcavity for each microchannel structure in the subset. Regarding this, for example, International Publication No. 02074438 (Gyros AB), International Publication No. 03018198 (Gyros AB), International Publication No. 03083108 (Gyros AB), International Publication No. 2005094976 (Gyros AB) and the like. You can refer to it. The volumetric microcavity is in communication with a downstream portion of the associated microchannel structure, such as a mixing microcavity, a reaction microcavity, a separation microcavity, and the like. Microchannel structures joined by a common inlet arrangement and / or common distribution manifold define a subset / subgroup of the microchannel structures of the device.

  Some inlet arrangements include a microcavity that does not provide volume-defining capability and is used only to initially receive a liquid fraction dispensed from the inlet port.

  The microcavities in the inlet array described above are U-shaped and may be provided with a lower portion that faces outward from the axis of rotation and is equipped with a valve function, generally a liquid outlet associated with a capillary valve. The liquid outlet can be used to transport the dispensed fraction into the downstream portion of the microchannel structure to which the inlet array is associated. For example, International Publication No. 0146465 (Gyros AB) can be referred to.

  A microcavity, such as a volumetric microcavity, a mixing microcavity, a reaction microcavity, etc., has a valve or flow regulating means that controls the flow deviation from the liquid discharged from the microcavity of interest. The valve is passive in this position, for example, the boundary between hydrophilic and hydrophobic surfaces (hydrophobic surface disruption) (WO 99585245 (Amersham Pharmacia Biotech AB). Utilizing changes in the chemical and / or geometric / physical surface characteristics (WO 98007019 (Gamera)) at the exit end, such as))). For preferred valves based on hydrophobic surface destruction, reference can also be made to WO 020774438 (Gyros AB), WO 04103890 (Gyros AB), and WO 04103891 (Gyros AB). The flow regulating means may be in the form of a porous bed, a membrane, other forms, or a relatively long and narrow microtube (regulated microtube). For this, reference can be made, for example, to International Publication No. 02075312 (Gyros AB) and International Publication No. 03025982.

  Reference can also be made to International Publication No. 02057775 (Gyros AB) and International Publication No. 02075776 (Gyros AB).

  The microfluidic device may also include other common microchannels / microtubes that connect different microchannel structures. A common channel / conduit containing various parts such as inlet ports, outlet ports, vents, etc. is considered as part of each mechanical structure with which they are common.

  Each microchannel structure is provided with at least one inlet opening for liquid and at least one outlet opening for exhausting excess air and possibly even excess liquid.

  The number of microchannel structures / devices is generally ≧ 10, for example ≧ 25, ≧ 90, ≧ 180, ≧ 270, ≧ 360. At least one, preferably two or more, eg all or a subset of the micromechanical structures on the device comprise at least one innovative unit herein.

  A sub-group of micromechanical structures comprises microchannel structures connected by a common function, such as a common inlet array common to 4-25 microchannel structures, for example. All microchannel structures of these subgroups essentially contain identical units (one or more) according to the invention (selected from units AF). The microchannel structures within these subgroups are generally functionally equivalent. That is, they are used in a time-parallel manner in connection with at least the innovative unit (s) that occur.

  Different principles can be utilized to transport liquid between one or more of the functional parts described above in a microfluidic device / microchannel structure.

  For example, as described in the following paragraphs, inertial force generated by rotating the disk can be used. Other effective forces include electromotive force and non-electromotive force such as capillary force and hydrostatic pressure.

Microfluidic devices are generally disk-shaped. The preferred shape is provided with a symmetrical (C _n ) axis perpendicular to or coincident with the disk plane. In the former case, n is an integer ≧ 2, 3, 4, 5 and preferably ∞ (C _∞ ). In the latter case, n is 2. In other words, the disc may be a rectangle such as a rectangle or other polygons. The disc may be circular. Once an appropriate disc shape has been selected, the liquid flow is then driven, for example, using centrifugal force generated by rotating the device around an axis of rotation perpendicular or parallel to the disc plane. The term “parallel” used in this description includes that the rotation axis coincides with the disk plane. In the variant most apparent on the priority date, the axis of rotation coincides with the axis of symmetry described above. International Publication No. 040550247 (Gyros AB) gives a preferred variant in which the axis of rotation is not perpendicular to the disk plane.

  In a preferred centrifugal force-based variant, each microchannel structure comprises an upstream section that is at a shorter radial distance than the downstream section with respect to the axis of rotation. By rotating the device around the rotation axis, the liquid is conveyed from the upstream section to the downstream section or into the meandering section of the unit F, for example, via the micro tubes I of the units A to E.

  A preferred device is a disk of similar size and shape as a conventional CD, for example, the size is related to a CD radius that is 10-300% of the conventional CD radius (about 12 cm). The upper and / or lower side of the disc may be flat or non-flat.

  The microchannel structure, or a component thereof, for example, the microtube I of the units A to E or the meandering part of the unit F, at least part of the microtube I of the units A to E or at least part of the meandering part of the unit F By an essentially flat substrate surface presenting defining exposed microstructures and by another essentially planar substrate surface presenting the rest of the microtube I and the rest of the serpentine Preferably it is manufactured. The coated form of the microtube or part thereof, or the coated form of the serpentine part or part thereof is obtained by juxtaposing the two substrate surfaces in parallel to define the desired structure. For example, International Publication No. 91016966 (Pharmacia Biotech AB), International Publication No. 01054810 (Gyros AB), International Publication No. 40524747 (Gyros AB), International Publication No. No. 030557790 (Gyros AB) can be compared. Both substrates are preferably made of a plastic material such as a plastic polymer material.

  The fouling property and hydrophobicity of the inner surface must be balanced according to the application. Regarding this, for example, International Publication No. 0147637 (Gyros AB) and International Publication No. 03086960 (Gyros AB) can be referred to.

  The terms “wetting” and “non-wetting” in relation to the inner wall take into account those having a water contact angle of ≦ 90 ° or ≧ 90 ° respectively on the inner surface of the inner wall. In order to facilitate efficient transport of liquid between different functional parts, the inner surface of each part preferably has a contact angle ≦ 60 °, for example ≦ 50 °, ≦ 40 °, ≦ 30 °, ≦ 20 °. It must be accompanied by wettability. These wettability values apply to at least one, two, three, four inner walls of the microtube. For example, if the water contact angle of one or more inner walls is larger than this due to its inherent non-wetting properties, it can be compensated by a smaller water contact angle of another inner wall (one or more). In particular, the wettability at the inlet array should be adapted to allow the aqueous liquid to fill the desired microcavity / microtube by capillary action (self-suction) once the liquid begins to enter the cavity with the inner surface dried. is there. The hydrophilic inner surface within the microchannel structure can limit one or more local hydrophobic surface breaks in the hydrophilic inner surface, eg, a passive valve, an anti-wicking function, venting as a vent opening to the surrounding air It may be provided as a function or other part. Regarding preferred hydrophobic surface destruction, International Publication No. WO99958545 (Gyros AB), International Publication No. WO02074438 (Gyros AB), International Publication No. 04103890 (Gyros AB), International Publication No. 04103891 (Gyros AB). ) Can be referred to.

  Liquids treated with innovative microfluidic devices, microchannel structures and units are generally aqueous and water miscible, which may contain one, two or more water miscible or water immiscible organic solutions Contains water mixed with a neutral solution. The above organic solutions include lower alcohols (methanol, ethanol, isopropanol, n-propanol, butanol, pentanol, etc., ethylene glycol, glycol, other liquid polyalcohols, etc.), N, N-dimethylformamide, dimethyl sulfoxide, acrylonitrile. , Dioxins, and lower acrylic polyesters such as dioxane and dimethoxyethylene. When mixing the plastic material to be treated, considerable care is taken that the apparatus is not dissolved, deformed or destroyed by the liquid to be treated.

  Innovative units, microchannel structures, and microfluidic devices can be used in life science assays such as receptor ligand assays such as immunoassays and nucleic acid assays, enzyme assays, cell-based assays, and the like. Typical variations of these types of tests are: International Publication No. 9955827, International Publication No. 0040750, International Publication No. 02075312, International Publication No. 03098022, International Publication No. 20040883108, International Publication No. 2004083109, International Publication No. 2004016926, International Publication No. 20066009506, PCT / SE2005 / 001887 (related to US SN11 “Microfluidic Assay and Microfluidic Device” dated December 12, 2006), PCT / SE2006 / 000071, PCT / SE2006 / 000072, etc. (all are Gyros AB / Gyros Patent AB). All of which are incorporated herein by reference.

Experimental Part Equipment Used The drawing illustrates a microchannel structure with all the functions of units A-F. This structure has been used to collect plasma from whole blood.

  The normal size of the device (1) shown in FIG. 1 is the same as a conventional CD having a diameter of 12 cm. From the size in FIG. 1, the width of each part of the microchannel structure can be calculated with the diameter of 12 cm in mind. The depth of each part is generally 100 μm, but may be narrower at certain locations (eg, packed particulate bed (row) (33), microchannel (42) in valve I (24)). A double depth / barrier to preserve the solid phase). The device (1) has 27 microchannel structures (2). This device is adapted to rotate around a rotation axis that passes through the center (3) of the device.

  This structure comprises an upstream microcavity I (4a + b) provided with a liquid inlet I (5) and a liquid outlet I (6). The liquid inlet I (5) is at the top (7) of the upstream microcavity, and the liquid outlet I (6) is at an intermediate position between the top (7) and bottom (8) of the upstream microcavity, Is divided into an upper part (4a) and a lower part (4b). The inflow microtube (8a) is connected to the liquid inlet I (5) at the top (7) of the upstream microcavity. The inflow microtube (8a) starts from the inlet port (9) (= opening provided in the surface of the device) above the height of the top (7) of the upstream microcavity (4a + b). An overflow opening (10) is provided at the same height as the liquid inlet I (5) of the inflow microtube (8a). The overflow opening (10) is connected to a downward overflow microtube (11) that allows the added extra liquid (liquid located above the overflow opening) to flow into the overflow microcavity (11a). . The overflow microcavity (11a) is provided with a vent (13) on the surface of the device (1). The lower / downstream part (4b) of the upstream microcavity (4a + b) is divided into two U-shaped finger microconduits (4b) below the height of the liquid outlet I (6). The downward portion of each finger microtube is narrowed / tapered (angle β) until bent upward (12). Each upward portion (12) terminates at a vent opening (14) provided in a portion of the surface of the device (1) above the height of the liquid inlet I (5). It is believed that the U-shaped, tapered finger microtube design reduces bubble containment during filling of the upstream microcavity (4a + b). By placing a valve / vent in the finger microtube in the shape of a non-wetting surface area (15a) (eg, finger ventilation unit C), a liquid opening on the surface of the device (1) (13 , 14) can be minimized. Placing these valves / vents below the height of the liquid outlet I (6) tends to increase the degree of control of the volume measurement performed in the upper part (4b) of the upstream microcavity (4a + b). Furthermore, the vent openings (13, 14) can also be arranged below the inlet port (9) and the overflow opening (10) liquid inlet I (5). The non-wetting surface area (15b) (valve) can also be arranged below the overflow microtube (11), for example at the connection with the overflow microcavity (11a) for similar reasons.

  The liquid outlet I (6) of the upstream microcavity is connected to the inlet end (16) of the microtube (17). The microtube terminates at the outlet end (18), which is much higher than the inlet end (16) (the height of the liquid outlet I (6)). In the structure shown, this outlet end (18) starts at the liquid inlet function (19) of the downstream microcavity II (20) and at the liquid inlet II (21) of the same downstream microcavity II (20). Part of a branch or intersection involving a terminating channel. The inlet end (16) of the microtube I (17) is at a higher position than the outlet end (18) and has an upward bend with an upper tip (22). A capillary valve (24), preferably a finger valve (unit C) of the type shown in FIG. 3, is provided in the upward section (23a) of the microtube I (17). If the position of the capillary valve I (24) is changed in the microtube I (17), especially in the upward section (23a) during the manufacture of the device, the rotational speed required for breakthrough can be easily changed. . The addition of a capillary valve I '(25) downstream of the capillary valve I (24) (as a non-wetting surface failure) provides the advantages described herein. If the upper tip (22) is placed above the height of the top (7) of the upstream microcavity (4a + b) and the capillary valve I (24) is placed below the height of the top (7), As described elsewhere, the advantage is obtained by separating the high density material from the low density material and separating each into a lower and upper phase.

  The downstream microcavity II (20) is provided with a number of liquid inlets II ′, II ″, II ′ ″ (25a, 26, 27) in addition to the liquid inlet II (21), as shown. Can do. Some of these (25a, 27) may be provided with a volume-defining unit including an overflow microtube (28, 29) terminating in an overflow microcavity (30, 31). In connection with the liquid outlet II (32) of the downstream microcavity, a capillary valve can be provided, or in the case of the illustrated arrangement, means can be provided to control the discharge of material from the microcavity (20). Therefore, a barrier (33) for constricting the lower part of the microcavity (20) is provided, and the particles can be collected in the form of a fine particle solid phase as a packed bed (34) with respect to this barrier (33).

A downstream microcavity II (20) may be provided with a transport microtube (35) leading to the detection microcavity, as defined for the unit F of the present invention. That is, the detection microcavity comprises an inlet portion (36), an outlet portion (37), and a microtube (39) defining a serpentine portion. As shown in the figure, the meandering portion may be oriented vertically upward (40), that is, in the longitudinal direction of the meandering portion, and the intermediate flow direction in the meandering portion actually moves the liquid in the meandering portion upstream. The direction is completely opposite to the centrifugal force (41) applied for the purpose. The serpentine has a number of continuous returns (r ₁ , r ₂ , r ₃ , r ₄ , r ₅ , r ₆ , r ₇ , r ₈ ...). Within each pair of adjacent returns (r ₁ , r ₂ ; r ₂ , r ₃ ; r ₃ , r ₄ ; r ₄ , r ₅ ...), an intermediate interval (r _1-2 , r _2-3 , r _3-4 , r _4-5 , r _5-6 , r _6-7 , r _7-8 ...), and in a preferred variant this is for example for each interval (r _1-2 , Similar to r _2-3 , r _3-4 , r _4-5 ...), every two sections (r _1-2 , r _3-4 ,...).

  This device is manufactured by attaching a lid to the bottom substrate, in which case the microchannel structure is duplicated by injection molding (WO 010554810 (Gyros AB)). Treatment (International Publication No. 0056808 (Gyros AB)) and introducing a non-wetting surface area locally (International Publication No. 99058245, International Publication No. 04103891 (Gyros AB)). The inner surface is coated with a nonionic hydrophilic polymer (International Publication No. 01047637 (Gyros AB)).

Modification A
The whole blood is separated into cell-free plasma using the microchannel structure (2) containing the separation microcavity (4a + b) (unit E). Whole blood is filled from the inlet port (9) to a height in the structure above the overflow opening (10). After separation, the plasma is conveyed to the row (34) through the microtube I (17) containing the finger valves (24) (units A to C). Inside the microtube I (17), the non-wetting surface (44) completely covers the microchannel (42) of the finger valve (24). During the filling of the separation microcavity (4a + b), the front meniscus of blood stops at the downstream end of valve I (24).

  To separate blood, the following rotation sequence is used: (i) 1000 rpm, 30 seconds, (ii) 1500 rpm, 180 seconds, (iii) 4000 rpm, 4 seconds, (iv) 2000 rpm, 10 seconds.

  Steps (i) and (ii) are used to separate red blood cells and white blood cells from the plasma. In this case, the first step further defines the blood volume by actuating the overflow microtube (11). In step (iii), in the microtube I (17), plasma-free cells are passed through the capillary valve (24) to the upper tip (22), and further to the downstream microcavity (reaction microcavity) (20), row (34). The final step (iv) is used to empty the upper part (plasma chamber) (4b) of the upstream microcavity (4a + b). The cell-free plasma is then rotated through the row for further processing.

Modification B
If the local non-wetting surface area (44b) is placed over the lower end (45) or within the finger / microchannel (42), the upper end (43) of the finger remains completely hydrophilic. As the liquid surface passes through the local non-wetting surface area of the valve, it is more likely to be capillary transported. This non-wetting positioning improves the efficiency of the separation, since higher rotational speeds and gravity are possible during the actual (to two-phase) separation step. For example: (i) 2000 rpm, 10 seconds, (ii) 4000 rpm, 50 seconds, (iii) 9000 rpm, 15 seconds, (iv) 0 rpm, 15 seconds, (v) 2000 rpm, 10 seconds. Blood is separated into a plasma portion and a cell portion using a rotational speed of 2000 to 9000 rpm. At a rotational speed of 9000 rpm, the plasma breaks the hydrophilic barrier of the valve (24). However, the plasma does not enter the drainage channel until the rotational speed is reduced to zero and the capillary force arrives in the drainage channel (downstream / lower section of microtube I (17)). Thereafter, when the rotational speed is increased to 2000 rpm, the liquid filling the drainage channel forms a drive plug and assists in emptying the plasma chamber.

Overview Certain innovative aspects of the invention are defined in more detail in the appended claims. Having described the invention and its advantages in detail, it should be understood that various changes, substitutions, and alternatives are possible without departing from the spirit and scope of the invention as defined by the appended claims. It is. Further, the scope of the present application is not limited to the specific embodiments of processes, machines, manufacture, compositions, means, methods, and steps described herein. As those skilled in the art will readily appreciate from the disclosure of the present invention, existing or later that can perform substantially the same function or achieve substantially the same results as the related embodiments described herein. The developed processes, machines, manufacture, compositions, means, methods, steps can be utilized in accordance with the present invention. Accordingly, the appended claims are intended to include within their scope processes, machinery, manufacture, compositions of matter, means, methods, or steps.

The microfluidic device which performed the actual experiment shown below is shown. FIG. 4 is an enlarged view of one of the microchannel structures. The enlarged view of the important part of unit C is shown. It is a lower part of the structure shown in FIG. This figure focuses on unit F.

Claims (13)

A microfluidic device (1) having a rotating shaft ,
(a) A microchannel structure (2) is included, and a detection microcavity (49) is provided in the microchannel structure (2). The detection microcavity (49) is a reaction generated in the microcavity (49) and / or in the reaction microcavity (20) located upstream of the detection microcavity (49). Is used to detect the results of and
(b) centrifugal force can be used to transport the liquid through the detection microcavity (49);
The detection microcavity (49) includes a detection microtube , and the detection microtube has a central portion between an inlet portion (36) and an outlet portion (37) and between the inlet portion and the outlet portion. The meandering microtube (39), the outlet of the meandering microtube being closer to the axis of rotation of the device than the entrance of the meandering microtube microfluidic device which is characterized in that there. 2. The microfluidic device according to claim 1 , wherein when the device is rotated, a longitudinal direction of the meandering microtube coincides with a direction of centrifugal force . It said meander to have a micro tube (39) is, two return adjacent to each other _{(r 1, r 2; r} 2, r 3, ...) intermediate section _(r 1-2 _{between, r 2-3} , ...) at least three return (r _{1, r} 2, _{r 3,} ...) microfluidic device according to claim 1 or 2, characterized in that it has a with a. The microfluidic device according to any one of claims 1 to 3, characterized by the following (a) and (b).
(a) micro tubes are the meandering (39) comprises at least three return _{(r 1, r 2, r} 3, ...) and,
(b) Each intermediate section includes a decompression unit in parallel with one or more corresponding decompression units of the other sections. Every other intermediate section (r _1-2 , r _3-4 ,... Or r _2-3 , r _4-5 ,...) Includes an extension, and the extension is one or more. The microfluidic device according to claim 4, wherein the microfluidic device is arranged so as to be parallel to a corresponding extension portion of another intermediate section . Each intermediate section (r _1-2 , R _2-3 , ...) includes an extension, wherein the extension is arranged to be parallel to a corresponding extension of one or more other intermediate sections. Microfluidic device. Every other intermediate section (r _1-2 , r _3-4 ,... Or r _2-3 , r _4-5 ,...) Always has a horizontal extension. Item 7. The microfluidic device according to any one of Items 3 to 6 . Subsequent return in the direction of flow (r ₁ , R ₂ , R ₃ , ...) the longitudinal position is the preceding return (r ₁ , R ₂ 8. The microfluidic device according to claim 1, wherein the microfluidic device is closer to the rotating shaft than a position in a longitudinal direction of. Any pair of consecutive returns (r ₁ , R ₂ ,; R ₂ , R ₃ ,; R ₃ , R ₄ ,; R ₄ , R ₅ , ...) between the first and second returns or any three pairs of consecutive returns (r ₁ , R ₂ , R ₃ R ₂ , R ₃ , R ₄ R ₃ , R ₄ , R ₅ 9. The microfluidic device of claim 8, wherein the increase in longitudinal position is constant between the first and third returns in (...). 10. The microfluidic device according to any one of claims 1 to 9 , wherein the detection microcavity comprises two or more serpentine microtubes coupled in series . Material between the at least one side of the inner wall and the microfluidic device of the detection micro-tube ultraviolet range, as in some wavelength range of 1~2000mm as in some of the infrared range and / or visible light region the microfluidic device according to any one of claims 1-10, characterized in that it is transparent to. 12. In the microfluidic device for detection (49) of a microfluidic device according to any one of claims 1 to 11, characterized in that it comprises the following steps (i) (ii) (iii) A method for detecting the result of a reaction occurring in a reaction microcavity (20) upstream of the microcavity (49).
(i) providing the microfluidic device;
(ii) step of transporting a liquid I required the detection microcavity (49) within the reaction and / or detection to be performed,
(iii) detecting the result in the detection microcavity; The method according to claim 12, characterized by the following (A) and (B).
(A) the reaction is part of the protocol that includes the detection microcavity (49) is filled with liquid II prior the step (iii),
(B) The step (iii) includes transferring the two liquids with the liquid II without mixing them with each other.

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