CN111359689A

CN111359689A - Micro-fluidic integrated system of multiunit oscillator pump

Info

Publication number: CN111359689A
Application number: CN202010363020.0A
Authority: CN
Inventors: 彭兴跃
Original assignee: Xiamen Qiyue Electronic Technology Co ltd
Current assignee: Xiamen Qiyue Electronic Technology Co ltd
Priority date: 2020-04-30
Filing date: 2020-04-30
Publication date: 2020-07-03
Anticipated expiration: 2040-04-30
Also published as: CN111359689B

Abstract

The invention discloses a micro-fluidic integrated system of a plurality of groups of vibrator pumps, which consists of a plurality of groups of vibrator pump micro-fluidic chips in a parallel or serial mode, wherein each group of micro-fluidic chip comprises a vibrator pump and a channel, and the vibrator pump consists of a spherical magneton with a definite NS pole arranged in the channel, a rectangular magnetic sheet with a definite NS pole arranged outside the channel and a driving coil. The micro-fluidic integrated control system can be widely used in a circulating system of cells or tissues, can completely simulate network tissues of a living body by series-parallel combination, is similar to a plastic culture dish channel, has the speed characteristic of being easy to calculate like a circuit, is easy to manufacture by a plastic injection mold, has low cost, small volume and portability, and plays an important role in the research of life science.

Description

Micro-fluidic integrated system of multiunit oscillator pump

Technical Field

The invention relates to the field of microfluidics, in particular to a microfluidic integrated system of a plurality of groups of oscillator pumps.

Background

The micro-fluidic chip adopts a micro-electro-mechanical processing technology similar to a semiconductor to construct a micro-channel system on the chip, transfers the experiment and analysis process to a chip structure consisting of a path and a small liquid-phase chamber which are mutually connected, loads a biological sample and a reaction liquid, and drives the flow of a buffer solution in the chip by adopting methods such as a micro-mechanical pump, an electric hydraulic pump, electroosmosis flow and the like to form a micro-channel so as to perform one or continuous multiple reactions on the chip.

The existing microfluidic systems have the problems of over-complex system, high price, large volume, no need of carrying at any time and detection at any time. It is therefore desirable to develop a microfluidic system that is inexpensive, small, easy to operate, does not worry about clogging the channels, has no life time limitations, is reliable and simple.

Disclosure of Invention

The invention provides a microfluidic integrated system of a plurality of groups of oscillator pumps, which aims to realize the functions of small volume, low cost and easy carrying of the microfluidic system.

The technical problem solved by the invention can be realized by adopting the following technical scheme:

the microfluidic integrated system of the multiple groups of oscillator pumps is composed of multiple groups of oscillator pump microfluidic chips in parallel or series connection, and is characterized in that: each group of micro-fluidic chips comprises a vibrator pump and a channel, wherein the vibrator pump consists of a spherical magneton with a definite NS pole arranged in the channel, a rectangular magnetic sheet with a definite NS pole arranged outside the channel and a driving coil.

Preferably, the channel is a three-dimensional channel or a two-dimensional channel, and the two-dimensional channel is any one or a combination of several channels in a two-in two-out mode, a two-in one-out mode and a one-in one-out mode.

Preferably, a tiny side channel is arranged beside the channel.

The invention integrates a plurality of groups of oscillator pump micro-fluidic chips into a micro-fluidic integrated system in a parallel or serial mode, each group of micro-fluidic is independently controlled by an independent oscillator pump, and simultaneously can be provided with a micro side channel, and can be widely used in a cell or tissue circulating system.

Drawings

Fig. 1 is a schematic diagram of the basic structure of the present invention.

Fig. 2 is a schematic diagram of a highly diversified pump, fig. 2a is a three-dimensional microfluidic, fig. 2 b-2 e are two-dimensional microfluidic, and fig. 2f is a schematic diagram of a horizontal placement of a vibrator pump.

Fig. 3 is a schematic diagram of an integrated array pump.

Fig. 4 is a graph comparing regression and geometric calculations.

FIG. 5 is a flow measurement of a lateral microchannel.

In the figure, 1 spherical magnet, 2 rectangular magnet pieces, 3 driving coils and 4 partition walls.

Detailed Description

The present invention will be described in further detail with reference to examples, but the embodiments of the present invention are not limited thereto.

Fig. 1 to 5 are preferred embodiments of the present invention, a microfluidic integrated system of the present invention is composed of a plurality of groups of oscillator pump microfluidic chips in parallel or in series, a single microfluidic chip mainly consists of an oscillator pump and a channel, the oscillator pump adopted in this embodiment is composed of a spherical magnet 1 with a definite NS pole as an oscillator, a rectangular magnet piece 2 with a definite NS pole and a driving coil 3; the spherical magneton 1 is placed in the fluid cavity, the rectangular magnet piece 2 and the driving coil 3 are used as driving bodies and are arranged outside the fluid cavity, namely, a partition wall 4 (also called a boundary) is arranged between the rectangular magnet piece 2 and the driving coil 3 and the spherical magneton 1. The rectangular magnet piece 2 is laid on the inner ring surface of the driving coil 3, and the driving coil 3 has the capability of driving the rectangular magnet 2 to rotate or swing. When the input current of the driving coil 3 is square wave current, the rectangular magnet piece 2 swings regularly with the center as a pivot, and the change of the magnetic force causes the spherical magnet 1 on the other side of the partition wall 4 to reciprocate in the direction parallel to the rectangular magnet piece 2. A spherical magnet 1 with the diameter of 2mm, a rectangular magnet piece 2 with the length of 4.5mm and a driving coil 3 with the inner ring width of 5mm and the length of 3mm can be adopted, the rectangular magnet piece 2 is placed in the driving coil 3, and the whole size of the whole vibrator pump does not exceed 1 cm.

The spherical magneton 1 is placed in an open channel, the rectangular magnet piece 2 and the driving coil 3 are placed outside the channel, and the vibrator pump sucks liquid from an inlet channel and outputs the liquid from an outlet channel. As shown in fig. 2. Three-dimensionally stable microfluidic fields, with inlet and outlet channels separated in different dimensional spaces, as shown in fig. 2a, all directions in the center of the x-y plane can be used as inlet channels, while the outlet channel can only use the positive or negative direction of the z-axis, leaving a large space for the inlet channel in the x-y plane even if the drive coil 3 occupies the positive y-axis. The vibrator pump is simplified into a two-dimensional space micro flow field, channel forms of 2 in and 2 out (figure 2b), 2 in and 1 out (figure 2c) and 1 in and 1 out (figure 2d) can be obtained, the 1 in and 1 out micro flow field of figure 2e can be obtained after the three types of channels are combined, and the strong magnetic force between the spherical magnet 1 and the rectangular magnet piece 2 can ensure that the micro flow pump can work at any angle, such as the vertical state of figure 2e, the horizontal state of figure 2f or the inversion state of figure 3. Different channels are combined together, so that a multi-group vibrator pump microfluidic integrated system can be integrated, and fig. 3 is an array pump microfluidic system integrated by a plurality of groups of same vibrator pumps.

The oscillator pump microfluidic system is quantitative or controllable, and fig. 4a shows the flow data for each channel at different frequencies. The flow (v) representing the pump output is proportional to the frequency (f). The drive signal is a square wave. This means that each time the spherical magneton 1 (i.e. the vibrator) moves to hit the liquid, it moves at the fastest possible speed. Higher frequency does not mean faster moving speed, it only means more hits in one second. When a small amount of liquid is delivered to the output channel in a fixed amount with each stroke of a cycle, the total amount of 1 second pumped into the output channel is proportional to the frequency.

vS_flow＝D_onecyclef (1)

Where v is the velocity, Sflow is the cross-sectional area, D is the output volume of one cycle, and f is the frequency.

The pumping mode of the vibrator pump is an integer, the frequency ratio of 1:1 is strictly followed, and the maximum stable frequency of the current system is less than 25 Hz. The frequency is higher if the force between the rectangular magnet piece 2 and the spherical magnet 1 is larger. The oscillator pump propels the fluid in integer pulses.

The velocity range of the main stream is about 400-10000 μm/s in the range of 1-25 Hz. The range rapidly extends to 5-10000 μm/s by means of a series of side channels (FIG. 4 a). But these parallel channels are not designed solely for speed reduction. As shown in fig. 4a, the regression curve not only has a high correlation coefficient, but also has good consistency. The slope (k) and its standard deviation (Sk) are calculated and plotted in fig. 4 b. Both fig. 4a and fig. 4b are the results of 1810 flow rate measurements. The perfect linear relationship between logarithmic speed and number of channels explains the ideal consistency of seven sets of data. Empirical model in equation 2 (fig. 4 b).

k＝389.3e^-0.5288c(2)

Where c is the channel number. The flow rate (v) is calculated by equation 3.

v＝389.3fe^-0.5288c(3)

For another fluid, similar parameters are shown (compare

equations

4 and 5 with equation 2).

y_chip1＝e^-0.5277c(4)

y_chip2＝e^-0.9468c(5)

Where y is the speed ratio of the first passage (c 0).

The microfluidic chip was converted to a circuit diagram and figure 4d is a circuit diagram simulating one chip. Each resistor (R1, R2, and R) is connected like a channel in the chip. In our model, the currents (I0-6) are the target parameters because they pass through a series of resistances R as if the liquid were flowing through the channel. To simplify the computation of I0-6, we add an infinite number of repeating electrical units (cn: R1, R2, R and In, n, to complete the translational symmetry and establish equation 6 (FIG. 4e) of the circuit diagram.

Where Rab (without first R) is the equivalent resistance without the left first R. In formula 7, Rab (without the first R) and In/In-1 are calculated from formulas 7 and 8, respectively.

For a real open microfluidic network (fig. 4f), the shortest distance between the two ends of the channel is measured if the width has a significant effect on the length. For fluid systems, equation 8 should be used with caution because the resistances (R1, R2, and R) are all invariants of the currents (I1, I2, and I). Even if the flow resistance is proportional to the length (L), we cannot simply replace R1, R2, and R with L1, L2, and L because the flow resistance increases with increasing flow. In a channel without a cover, too fast a flow rate may cause the water level to expand. More complexly, the shape of the flow surface, which is limited by surface tension, may change with the wave generated by the vibrator. With all these uncertainties, the flow (v) is predicted only by geometric measurements and equation 8 or 9 derived from the electrical diagram (fig. 4 g).

The error between the predicted value and the measured value is less than 0.068% (0.5896-0.5900 and 0.5893). The high-precision prediction proves that the resistance model is suitable for the micro-fluidic system of the vibrator pump.

As the thickness of the capillary vessel can reach 6-8 μm, when the open channel becomes thin, the prediction model is still available. A tiny U-shaped channel is made beside the main channel (fig. 5a), with both the inlet and the outlet connected to the main channel. The pressure differential between the upstream and downstream streams pushes the liquid into the tiny side channels. The flow speed in the flow channel is far lower than that in the main flow channel, so the side flow channel side speed reducer is called. The flow rate is proportional to the width (W), the distance (M) of the U-shaped ends or the inverse of the length (L) at the same depth of all the side channels.

Only one of the three parameters (W, M and L) was varied in each experiment (fig. 5 b). The water flow in the lateral ditches is stable (fig. 5 c); the flow rate is proportional to W, M and 1/L (FIG. 5 d-f). This lateral design provides a fast way to reduce the flow rate (estimated by equation 10) and the vibrator pump can deliver the liquid stably to the depth of the micro channel.

The micro-fluidic integrated system is more perfect due to the addition of the side channel, can cope with different channel conditions after being integrated in various different channel forms, can be widely applied to a circulating system of cells or tissues, is used for researching complex network tissues of a living body, each group of oscillator pumps is equivalent to a valve, can completely simulate the network tissues of the living body through series-parallel combination, and plays an important role in the research of life science. And the micro-fluidic chip is similar to a plastic culture dish channel, the speed characteristic of the micro-fluidic chip is easy to calculate like a circuit, and the micro-fluidic chip is easy to manufacture by using a plastic injection mold. During the culture process, the spherical magnetons 1 are easily added and moved, and are taken out like a culture medium. Therefore, the microfluidic system is cheap like a culture dish, small like a bead, programmed like a list, power consumption like a headset, microliter scale cycle without dead zones, and conventional operation technique.

The above description is only a preferred embodiment of the present invention, and is not intended to limit the technical scope of the present invention, so that any minor modifications, equivalent changes and modifications made to the above embodiments according to the technical spirit of the present invention still belong to the protection scope of the present invention.

Claims

1. The microfluidic integrated system of the multiple groups of oscillator pumps is composed of multiple groups of oscillator pump microfluidic chips in parallel or series connection, and is characterized in that: each group of micro-fluidic chips comprises a vibrator pump and a channel, wherein the vibrator pump consists of a spherical magneton with a definite NS pole arranged in the channel, a rectangular magnetic sheet with a definite NS pole arranged outside the channel and a driving coil.

2. The microfluidic integrated system of multiple group oscillator pumps of claim 1, wherein: the channel is a three-dimensional channel or a two-dimensional channel, and the two-dimensional channel is any one or combination of two-in two-out, two-in one-out and one-in one-out.

3. The microfluidic integrated system of multiple group oscillator pumps of claim 1, wherein: and a tiny side channel is arranged beside the channel.