CN110684828A

CN110684828A - Digital PCR chip, digital PCR detection system and detection method

Info

Publication number: CN110684828A
Application number: CN201810738786.5A
Authority: CN
Inventors: 周阳; 李昂
Original assignee: Beijing Raining Biology Technology Co Ltd
Current assignee: Beijing Raining Biology Technology Co Ltd
Priority date: 2018-07-06
Filing date: 2018-07-06
Publication date: 2020-01-14

Abstract

The invention discloses a digital PCR chip, a digital PCR detection system and a detection method, wherein the digital PCR chip comprises a chip body with a liquid drop storage cavity, a liquid inlet arranged on the chip body, an accommodating cavity vertically arranged on the chip body and communicated with the liquid inlet, and a liquid outlet arranged on the chip body; the chip body further comprises a first channel and a second channel, the first channel is used for communicating the liquid inlet with the liquid drop storage cavity, the second channel is used for communicating the liquid outlet with the liquid drop storage cavity, the first channel is provided with a first inner channel located inside the chip body, and the second channel is provided with a second inner channel located inside the chip body. The liquid drops are generated in the accommodating cavity and then enter the liquid drop storage cavity through the liquid inlet and the first channel, the liquid drops can keep good stability and closure in the conveying process, uniform single-layer or multi-layer tiling of the liquid drops in the liquid drop storage cavity is realized, and the detection result which is more accurate is obtained obviously.

Description

Digital PCR chip, digital PCR detection system and detection method

Technical Field

The invention relates to a digital PCR chip, a digital PCR detection system and a detection method.

Background

The Polymerase Chain Reaction (PCR) technology is one of the most important tools in modern biology, and is widely applied to medical diagnosis, individualized medicine, food inspection, transgenic biological detection, pathogen identification, immunoassay, forensic science and the like. And as the latest generation of PCR technology, digital PCR (dPCR) generated based on the development of microfluidic technology has smaller reaction volume, faster reaction speed, lower system noise and higher sensitivity than the traditional qPCR.

The droplet Digital PCR (Droplet Digital PCR) technology is a water-in-oil droplet technology based on a microfluidic chip, single DNA molecules are packaged into individual droplets through a water-in-oil structure, mutual isolation among the DNA molecules is realized by using the inertia of oil, and each DNA molecule is limited in the droplet to be amplified independently, so that competition from other sequences is avoided. After the amplification of DNA molecules is completed under the appropriate temperature condition, the accurate quantification of the DNA copy number can be realized by utilizing a Poisson distribution algorithm by recording the total number of droplets and the number of droplets in which a fluorescent signal can be detected.

One of the core technologies of micro-liquid operation is to divide micro-liter liquid into micro-reaction systems with volume of nano liter or even pico liter. One major technical branch of the formation of microreaction systems is the formation of emulsified microdroplets. In recent years, various techniques for generating micro-droplets such as membrane emulsification, spray emulsification, microfluidic chip method, micro-channel injection/ejection method, etc. have been reported in the literature. The recent chinese patent application publication No. CN104815709A and chinese patent No. ZL201410655191.5 further optimize the method of generating emulsified micro droplets through micro-channels. These methods of emulsifying microdroplets have certain disadvantages in practical applications. The method of the invention of Chinese patent No. ZL201410655191.5 utilizes the interface energy and the fluid shearing force of trace liquid during the gas-liquid phase interface conversion to overcome the surface tension and the adhesive force of the liquid at the outlet of the micro-channel, so that the liquid drops flowing out of the orifice of the micro-channel can smoothly separate from the micro-channel and form liquid drops with controllable size in the immiscible liquid. However, this method requires the micro-pipe to perform a cutting motion up and down on the liquid surface, and requires high-precision positioning of the micro-pipe relative to the start and end positions of the liquid surface, which is difficult in engineering implementation. The method of chinese patent application publication No. CN104815709A cuts off the injected immiscible liquid to form droplets by the shearing force generated by the uniform motion of the micro-pipe in the liquid, but this method has a great influence on the size of the droplets generated by the micro-pipe due to various system factors (such as viscosity of the liquid, temperature of the environment, motion speed, motion trajectory, etc.), and this error is accumulated as the number of the generated droplets increases, so the control of the uniformity of the volume size generated by the large-batch droplets is difficult.

In the prior art, some digital PCR chips collect and store liquid drops and generate liquid drops, so that the liquid drops can be directly used for detection after being collected, however, the chips with the structures are difficult to stably generate the liquid drops or the stability and the uniformity of the liquid drops are poor; the chip has small detection flux and can not meet the requirements of clinical automation and high-flux liquid drop analysis in unit area; in addition, the chip has the advantages of complex structure, high processing precision requirement and high cost.

Disclosure of Invention

The present invention is directed to an improved digital PCR chip to address one or more of the deficiencies of the existing PCR chips.

The invention also provides a digital PCR detection system and a detection method based on the digital PCR chip.

In order to achieve the purpose, the invention adopts a technical scheme that: a digital PCR chip comprises a chip body with a liquid drop storage cavity, a liquid inlet arranged on the chip body, an accommodating cavity vertically arranged on the chip body and communicated with the liquid inlet, and a liquid outlet arranged on the chip body; the chip body further comprises a first channel and a second channel, the first channel is used for communicating the liquid inlet with the liquid drop storage cavity, the second channel is used for communicating the liquid discharge port with the liquid drop storage cavity, the first channel is provided with a first inner channel located inside the chip body, and the second channel is provided with a second inner channel located inside the chip body.

According to some preferable schemes of the invention, the accommodating cavity extends upwards from the upper surface of the chip body, and the liquid inlet is positioned at the bottom of the accommodating cavity.

According to some preferred embodiments of the present invention, the receiving cavity has a length of 2 ~ 30mm, a width of 2 ~ 30mm, and a height of 20 ~ 2000 um.

According to some preferred schemes of the invention, the accommodating cavity and the chip body are integrally formed, or the accommodating cavity and the chip body are fixedly connected.

According to some preferred aspects of the invention, the first channel communicates at an end with the droplet storage chamber; and/or the second channel communicates at an end with the droplet storage chamber.

According to some preferred aspects of the invention, the first channel is located on one side of the droplet storage chamber; and/or the second channel is located to one side of the droplet storage chamber.

According to some preferred aspects of the present invention, the first internal passage and the second internal passage are provided on different sides of the droplet storage chamber.

According to some preferable forms of the present invention, the droplet storage chamber has a first communication port communicating with the first passage, and a second communication port communicating with the second passage, the first communication port and the second communication port being provided on opposite sides of the droplet storage chamber.

Further, the first communication port is arranged right opposite to the second communication port.

According to a further embodiment of the present invention, the droplet storage chamber has at least one arc-shaped chamfer, and the first communication port is provided at the arc-shaped chamfer.

According to a further embodiment of the invention, the droplet storage chamber is polygonal with an inner rounded chamfer; alternatively, the droplet storage chamber is circular or elliptical.

According to a further embodiment of the present invention, the droplet storage chamber is square or rectangular, the first communication port and the second communication port are provided at opposite corners of the droplet storage chamber, the first internal passage and the second internal passage are provided at opposite sides of the droplet storage chamber, and the first internal passage and the second internal passage are respectively communicated at end portions with the first communication port and the second communication port.

According to some preferred aspects of the invention, a portion or the entirety of the first channel, the second channel is curved.

Further, the first channel comprises at least one straight extending section and at least one arc extending section, one end of the straight extending section is communicated with the liquid inlet, and the inner space of the at least one straight extending section and the inner space of the at least one arc extending section form the first inner passage.

According to a further embodiment of the present invention, the first inner passage is formed by an inner space of a straight extension section and an arc extension section, the straight extension section is located outside the droplet storage chamber and is parallel to one side of the droplet storage chamber, one end of the straight extension section is bent toward the droplet storage chamber and extends to form the arc extension section, and an end of the arc extension section away from the straight extension section is communicated with the droplet storage chamber.

In a preferred embodiment, the droplet storage chamber, the first channel and the second channel form a centrosymmetric structure.

According to some preferred embodiments of the present invention, the first channel, the second channel, and the bottom surface of the droplet storage chamber are located at the same height position.

According to some preferred aspects of the invention, the liquid inlet is higher than the first channel in height in the vertical direction, and/or the liquid outlet is higher than the second channel in height in the vertical direction.

According to the invention, the inner diameter of the liquid inlet may be, for example, 4mm to 8 mm.

According to the invention, the height of the liquid inlet may be, for example, 5mm to 15 mm.

According to the invention, the height of the droplet storage chamber may be, for example, 50-1000 um. The length and width may be, for example, 5 to 30mm, respectively.

According to the invention, the inner diameters of the first channel and the second channel may be, for example, 4mm to 10mm, respectively.

According to the invention, the thickness of the chip body is 1 ~ 6 mm.

According to some preferred embodiments of the present invention, the droplet storage chamber has a square cross section, and the side length of the square is 2 to 30 mm; the height of the liquid drop storage cavity is 20-2000 um.

According to some preferred aspects of the present invention, the chip further comprises a sealing cover for sealing the accommodation cavity.

Further, the accommodating cavity is provided with a plurality of accommodating cavities, correspondingly, the sealing covers are also provided with a plurality of accommodating cavities, and all the sealing covers are integrally arranged on one integral component.

According to some preferred embodiments of the present invention, the digital PCR chip further comprises a drain tube vertically disposed on the chip body, and the drain tube is communicated with the drain port.

According to some preferred embodiments of the present invention, the drain pipe extends upward from the upper surface of the chip body, and is integrally formed with or fixedly connected to the chip body.

According to some preferable schemes of the invention, the liquid outlet is provided with a negative pressure joint which is used for being matched and connected with an outlet of a negative pressure device.

According to some preferable schemes of the invention, the chip body is formed by overlapping a chip cover plate and a chip substrate along the thickness direction, the chip cover plate is a flat plate, a groove is formed on the chip substrate, and the flat plate and the groove are overlapped and compressed with each other to form the liquid drop storage cavity, the first channel and the second channel.

According to a further embodiment of the present invention, the opening of the groove faces downward, the chip substrate is located above the chip cover plate, and the chip cover plate is a transparent glass plate, a transparent PC plate, a transparent acrylic plate, a COP transparent plate, or a black non-reflective plate.

According to another embodiment of the invention, the opening of the groove faces upwards, the chip substrate is positioned below the chip cover plate, and the chip substrate and the chip cover plate are respectively made of plastics.

According to a preferred embodiment of the present invention, the droplet storage chamber, the first channel, and the second channel together constitute a chip unit, and the chip body is provided with a plurality of the chip units.

According to a further embodiment of the present invention, the chip body is elongated, and the plurality of chip units are distributed along a length direction of the chip body.

The invention also provides a digital PCR detection system, which comprises a digital PCR detection device, the digital PCR chip and a negative pressure device matched with the digital PCR chip for use, wherein the negative pressure device is used for generating negative pressure in the first channel, the liquid drop storage cavity and the second channel.

The invention also provides a digital PCR detection method based on the digital PCR chip or the digital PCR detection system, which comprises a loading step of delivering liquid drops to the liquid drop storage cavity, wherein the loading step comprises the following steps:

filling oil phase into a liquid drop storage cavity, a first channel, a second channel and an accommodating cavity of the digital PCR chip;

injecting water phase into the oil phase in the accommodating cavity by using a micro-pipeline, and enabling the micro-pipeline to swing in a reciprocating manner while injecting the water phase, so that liquid drops are formed in the accommodating cavity;

and the liquid drops are conveyed to the liquid drop storage cavity through the liquid inlet and the first channel.

According to some preferred embodiments of the present invention, the droplet storage chamber, the first channel, and the second channel are filled with an oil phase before the water phase is injected.

According to some preferred embodiments of the present invention, after filling the oil phase and before injecting the water phase, the liquid inlet and the liquid outlet are kept in a sealed state, and the PCR chip is allowed to stand horizontally for more than 5 min.

According to some preferred aspects of the present invention, after the formation of the liquid droplets is started or after the generation of the liquid droplets is completed, the negative pressure means is turned on to promote the discharge of the oil phase from the liquid discharge port and the flow of the liquid droplets to the liquid droplet storage chamber.

According to the present invention, the "oil phase" and the "aqueous phase" have the general meaning in the art, and are not particularly limited. The oil phase is generally less dense than the water phase.

Due to the application of the technical scheme, compared with the prior art, the invention has the following advantages: the structure design of the digital PCR chip is based on the design principle completely different from that of the traditional digital PCR chip, the accommodating cavity on the chip body of the digital PCR chip forms a generating container for generating liquid drops, the liquid drops are deposited in the liquid inlet by self gravity after being generated in the accommodating cavity and then gradually enter the liquid drop storage cavity through the first channel, and meanwhile, the liquid drops keep good stability in the conveying process and are uniformly paved in the liquid drop storage cavity through the structure design of the first channel, the second channel and the liquid drop storage cavity on the chip, so that the digital PCR chip is beneficial to obtaining a more accurate detection result and has the remarkable advantages of simple structure and low cost. Furthermore, based on the digital PCR chip structure and the method, the liquid drops can be tiled in a multilayer manner in the liquid drop storage cavity, the detection flux is greatly improved, and the requirements of clinical automation and high-flux liquid drop analysis in unit area are met.

The digital PCR detection system and the detection method have the advantages of high detection flux, more accurate detection result and the like.

Drawings

FIG. 1 is a schematic structural diagram of a micro-droplet generating device used in the present invention;

FIG. 2 is a schematic view of the reciprocal oscillation of a micro-droplet generator used in the present invention;

FIG. 3 is a schematic view of the micro-droplet generation apparatus employed in the present invention;

FIG. 4 is a schematic view of a prior art arrangement without the microchannel being associated with any vibration motor;

FIG. 5 is a schematic view of a prior art micro-pipe mounted on a vibration motor capable of generating a uniform linear motion;

FIG. 6 is a schematic view of a micro-channel mounted on a rotatable driving mechanism in a micro-droplet generator according to the present invention;

FIG. 7 is a schematic diagram of analysis of relevant factors affecting microdroplet generation;

FIG. 8 is a front view of an embodiment micro-droplet generation apparatus;

FIG. 9 is a front cross-sectional view of an embodiment of a micro-droplet generation apparatus;

FIG. 10 is a left side view of an embodiment micro-droplet generation apparatus;

FIG. 11 is a rear view of an embodiment micro-droplet generation apparatus;

FIG. 12 is a cross-sectional view taken at A-A of FIG. 11;

FIG. 13 is an enlarged view of a portion of FIG. 12 at C;

FIG. 14 is an enlarged view of a portion of FIG. 12 at D;

FIG. 15 is a cross-sectional view taken at B-B of FIG. 12;

FIG. 16 is a rear view of another embodiment of a micro-droplet generation apparatus useful in the present invention;

FIG. 17 is a front cross-sectional view of another embodiment of a micro-droplet generation apparatus useful in the present invention;

FIG. 18 is a front view of another embodiment of a micro-droplet generation apparatus useful in the present invention;

FIG. 19 is a left side view of another embodiment of a micro-droplet generation apparatus useful in the present invention;

FIG. 20 is a schematic diagram of a motor for closed-loop control of vibration angle or position as is involved in a droplet generator for use in the present invention;

FIG. 21 is a schematic structural diagram of embodiment 1 of the digital PCR chip system of the present invention;

FIG. 22 is an exploded view of the digital PCR chip system of embodiment 1 according to the present invention;

FIG. 23 is a front view of a chip substrate in the digital PCR chip of example 1;

FIG. 24 is a schematic sectional view taken along the line M-M in FIG. 23;

FIG. 25 is a top view of the chip body of FIG. 23;

FIG. 26 is a bottom view of the chip body of FIG. 23;

FIG. 27 is a schematic view showing the structure of a sealing cap in the digital PCR system of example 1;

FIG. 28 is a first schematic diagram of an exploded structure of embodiment 2 of the digital PCR chip system of the present invention;

FIG. 29 is a second schematic exploded view of embodiment 2 of the digital PCR chip system of the present invention;

FIG. 30 is an isometric view of a chip cover plate in the digital PCR chip of example 2;

FIG. 31 is a front view of the chip cover plate of FIG. 30;

FIG. 32 is a schematic sectional view taken along the line N-N in FIG. 31;

FIG. 33 is a bottom view of the chip cover plate of FIG. 30;

FIG. 34 is a top view of the chip cover plate of FIG. 30;

FIG. 35 is an isometric view of a chip substrate in the digital PCR chip of example 2;

FIG. 36 is a top view of FIG. 35;

figures 37 to 39 are schematic views of the spreading of droplets as they enter the droplet storage chamber via the first channel;

FIG. 40 is a schematic top view of a droplet in a flat configuration in a droplet storage chamber;

fig. 41 and 42 are schematic diagrams showing the liquid drops in two layers and three layers in a flat state in the liquid drop storage cavity.

Detailed Description

The technical solution of the present invention is further explained with reference to the drawings and the specific embodiments.

First, the detailed structure and operation principle of the droplet generating device used in the present invention will be described in detail with reference to the embodiments and the drawings. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.

The invention provides a novel liquid drop generating system and a generating thought. The droplet generation system integrates droplet formation and detection. The basic structure of the liquid drop generating system provided by the invention comprises a micro-pipeline, a rotary driving mechanism and a PCR chip, and the parts except the PCR chip are also called a liquid drop generating device in the invention. The liquid drop generating system of the invention can generate liquid drops with uniform volume and size in large batch, and the liquid drops can be directly used for detection.

As shown in fig. 1, there are shown a micro-pipe 100 of a liquid droplet generating system, a rotary driving mechanism 200, etc., the micro-pipe 100 having a first opening 110 for outputting a first liquid 130, the rotary driving mechanism 200 for driving the micro-pipe 100 to make a horizontal reciprocating swing. As shown in fig. 2, the rotation driving mechanism 200 drives the micro-pipe 100 to oscillate back and forth around the rotation center 221, so that the first opening 110 of the micro-pipe 100 also oscillates back and forth, thereby generating the micro-droplets 131 under the liquid surface of the second liquid 610.

As shown in fig. 1, in order to enable the first opening 110 of the micro-pipe 100 to continuously generate the micro-droplets 131, the micro-droplet generating device further comprises a fluid driving mechanism 300, and the fluid driving mechanism 300 is communicated with the second opening 120 of the micro-pipe 100 through a delivery pipe 310. The second opening 120 of the micro-pipe 100 is communicated with the first opening 110, and the fluid driving mechanism 300 can apply a stable driving force to the interior of the micro-pipe 100 through the delivery pipe 310, so that the first liquid 130 in the micro-pipe 100 can stably and continuously flow out of the first opening 110 and generate the micro-droplets 131.

The method for generating the liquid drops is a very complex dynamic process, and a plurality of factors influence the volume of the generated liquid drops. The main factors are: surface tension of the droplet (related to the difference in surface energy between the first and second liquids, the microchannel opening area), adhesion between the microchannel opening and the droplet (influenced by the channel opening size and surface properties); shear forces (determined by the viscosity of the second liquid, the velocity of the microchannel motion and the droplet surface area), centrifugal forces (related to the mass of the droplet, the radial acceleration of the oscillation of the microchannel), and tangential inertial forces (proportional to the tangential acceleration of the oscillation of the microchannel and the droplet mass). Centrifugal force is essentially radial inertial force.

As shown in fig. 3, since the first opening 110 of the micro-pipe 100 is driven by the rotation driving mechanism 200 to generate a rotation motion, the micro-droplets 131 formed by the first liquid 130 in the micro-pipe 100 at the orifice of the first opening 110 of the micro-pipe 100 are separated from the orifice of the first opening 110 of the micro-pipe 100 under the liquid level of the second liquid 610 by the combined action of the shear force determined by the viscosity of the second liquid 610, the velocity of the movement of the orifice of the first opening 110 of the micro-pipe 100 and the surface area of the micro-droplets 131, the centrifugal force related to the mass of the micro-droplets 131 and the swing radial acceleration of the orifice of the first opening 110 of the micro-pipe 100, and the tangential inertial force proportional to the swing tangential acceleration of the orifice of the first opening 110 of the micro-pipe 100 and the mass of the micro-droplets 131.

The following compares the reciprocating swing mode (see fig. 6 to 7) of the droplet generating apparatus used in the present invention with other modes (see fig. 4 to 5) to describe the specific technical effects obtained by the present invention. It should be noted that all the following analysis is performed by taking the first liquid 130 droplet flowing out of the micro-channel as an independent object, and the first liquid 130 droplet is shown as an independent system by a dashed box in fig. 4-7.

Fig. 4 is a schematic view of a prior art situation in which the micro-duct is not connected to any vibration motor. In the prior art, when the fluid driving device continuously injects the first liquid 130 into the second liquid 610 through the micro-pipe 100 at a constant speed, the droplet will gradually increase. Because the liquid volume is not compressible, under the condition of uniform injection, the liquid drop volume is also increased at a uniform speed. Acting on the droplets are surface tension and adhesion forces that keep the droplets from falling off, in addition to downward gravitational forces. When the drop grows to a critical volume (see volume shown by the cut line in fig. 4), it falls off by gravity against surface tension and adhesion. This method cannot generate microdroplets characterized by nanoliters because the droplets must grow to the microliter level of gravity to be able to overcome the tension and adhesion forces.

Fig. 5 is a schematic view of a prior art micro-pipe fixed to a vibration motor capable of generating a uniform linear motion. As shown in fig. 5, in the prior art, when the fluid driving device continuously injects the first liquid 130 into the second liquid 610 through the micro-pipe 100 at a constant speed, the droplet will gradually increase. Because the liquid volume is not compressible, under the condition of uniform injection, the liquid drop volume is also increased at a uniform speed. Unlike the situation shown in fig. 4, the linear motor is simultaneously operated to drive the micro-pipe 100 to perform a uniform leftward linear motion. The force profile of the droplet is then as shown in fig. 5, and the droplet is subjected to a shear force to the right due to the relative motion between the droplet and the second liquid 610, which is positively correlated to the velocity and surface area of the droplet. Thus at a constant velocity, this force increases as the drop volume increases. Gravity is much less than shear and is ignored. At a certain critical volume (see FIG. 5 for a cut line), it is the moment when the droplet separates from the microchannel orifice when the shear forces overcome the surface tension and the adhesion forces. This critical volume will be disturbed up and down due to environmental and system fluctuations, which is the main factor causing the droplet size to be non-uniform (see dashed line a in fig. 7). The error caused by this disturbance is very large at such uniform motion (this problem is present in the prior art, such as the microchannel droplet generation technique of fig. 4-5 and the prior patent mentioned in the background section).

FIG. 6 is a schematic view of the micro-channel being fixed to a rotatable driving mechanism in the micro-droplet generator of the present invention. As shown in fig. 6, when the fluid driving device continuously injects the first liquid 130 into the second liquid 610 through the micro-pipe 100 at a constant speed, the variation of the speed of the micro-pipe 100 has a high frequency modulation due to the high frequency oscillation, so that the drop experiences a break-away force having a high frequency modulation. The resultant centrifugal force is a combination of shear, centrifugal and tangential inertial forces. When there is a disturbance at the critical point, the high frequency variation of the drop-out force is sufficient to break through the disturbance at the critical point in a very short time, so as to minimize the volume error caused by the disturbance (since the volume of the droplet is increased at a constant speed by the fluid driving device, the small time required for breaking through the critical disturbance means the small volume error). As shown in fig. 7, it can be clearly seen that under the same critical disturbance, the volume error 1 generated by the swing of the micro-pipe fixed on a motor capable of reciprocating swing is much smaller than the volume error 2 generated by the uniform speed.

As shown in fig. 8, 9 and 10, as a preferred embodiment, the rotation driving mechanism 200 of the droplet generating device of the present invention includes a rotation motor 210, a rotation shaft 220, and a joint 230, wherein an output end of the rotation motor 210 is connected to the rotation shaft 220, the joint 230 is fixedly connected to the rotation shaft 220 along a direction perpendicular to an axis of the rotation shaft 220, and the microchannel 100 is mounted on the joint 230. The rotating motor 210 can drive the rotating shaft 220 and the joint 230 to rotate and swing around the axis of the rotating shaft 220, so as to drive the micro-pipe 100 to swing back and forth. The rotary driving mechanism 200 of the droplet generating apparatus of the present invention may be other rotary driving devices such as a swing cylinder and a rotary electromagnet.

In this embodiment, the microchannel 100 has a tubular structure with openings at both ends, and the joint 230 is also tubular for facilitating the installation of the microchannel 100, and as shown in fig. 13, the tubular joint 230 has a third opening 231 and a fourth opening 232 communicating with each other inside, the duct 310 is connected to the third opening 231, and the second opening 120 of the microchannel 100 is connected to the fourth opening 232. The fluid driving force output by the fluid driving mechanism 300 can stably act on the micro-pipe 100 through the delivery pipe 310 and the joint 230, so that the first liquid 130 in the micro-pipe 100 can stably and continuously flow out from the first opening 110 to form the micro-droplets 131.

Since the micro-droplet generating device of the present invention can be used in the field of biological detection, in order to avoid cross contamination of biological materials, the micro-tube 100 is usually disposable, so that the micro-tube 100 after each use needs to be detached from the connector 230, in order to improve the detaching efficiency, the micro-droplet generating device of the present invention further comprises a needle withdrawing mechanism 400, as shown in fig. 12 and 13, the needle withdrawing mechanism 400 comprises a needle withdrawing plate 410 and a needle withdrawing plate driving assembly 420, the needle withdrawing plate 410 is provided with a needle withdrawing hole 411, the needle withdrawing hole 411 is sleeved outside the connector 230, the second opening 120 of the micro-tube 100 is sleeved outside the fourth opening 232 and is opposite to the needle withdrawing plate 410, the needle withdrawing plate driving assembly 420 is used for driving the needle withdrawing plate 410 to move towards the micro-tube 100, when the needle withdrawing plate 410 abuts against the second opening 120 of the micro-tube 100, an extrusion force is applied to the micro-tube 100 to detach it from the connector 230, continued movement of the pin extractor plate 410 pushes the micro-pipe 100 out of the fitting 230. thereafter, the pin extractor plate drive assembly 420 drives the pin extractor plate 410 to move closer to the delivery tube 310 so that the next micro-pipe 100 can be fitted over the fitting 230. In addition to the needle withdrawing mechanism provided in this embodiment, other structures may be adopted to separate the micro-pipe from the joint, for example, a jaw is used to clamp the micro-pipe, and the micro-pipe is pulled from the joint by driving the jaw to move so as to separate the micro-pipe from the joint.

As a preferred embodiment, in order to facilitate the installation and removal of the micro-pipe 100, the outer portion of the fourth opening 232 of the joint 230 is in a truncated cone shape with a large top and a small bottom, so as to reduce the resistance of the installation and removal of the micro-pipe 100.

Specifically, the needle withdrawing plate driving assembly 420 comprises a needle withdrawing plate driving motor 421, a first lead screw 422 and a first lead screw nut 423, the needle withdrawing plate driving motor 421 is fixedly mounted on the mounting bracket 240, the output end of the needle withdrawing plate driving motor 421 is connected with the first lead screw 422, the first lead screw nut 423 is mounted in a matching manner with the first lead screw 422, and the needle withdrawing plate 410 is connected with the first lead screw nut 423. First lead screw nut 423 and first lead screw 422 cooperate to change the rotary motion of withdrawing needle board driving motor 421 output into first lead screw nut 423 along the ascending rectilinear motion of first lead screw 422 axial to can drive withdrawing needle board 410 and carry out rectilinear motion, of course, can also adopt the rectilinear drive assembly of other forms to drive withdrawing needle board 410. Such as a cylinder drive.

Referring to fig. 18, the needle withdrawing plate driving assembly 420 of another embodiment includes a first cylinder 1421 and a first fixing nut 1423, the first cylinder 1421 is fixedly mounted on the mounting bracket 240, the first fixing nut 1423 is mounted to the front end of the piston rod 1422 of the first cylinder 1421 in a matching manner, and the needle withdrawing plate 410 is connected to the first fixing nut 1423. When gas is injected into the first cylinder 1421, the front end of the first cylinder rod 1421 extends outward and moves axially along the rod. The first fixing nut 1423 is matched with the front end of the piston rod of the first cylinder 1421 to transmit the axial motion output by the first cylinder 1421 to the needle withdrawing plate 410, so that the needle withdrawing plate 410 can be driven to perform linear motion to withdraw the needle.

Further, the rotary driving mechanism 200 further includes a mounting bracket 240, the rotary motor 210 and the needle withdrawing plate driving motor 421 are respectively and fixedly mounted on the mounting bracket 240, and two ends of the rotary shaft 220 are rotatably disposed in the mounting bracket 240 through bearings, so that the structure of the rotary driving mechanism 200 can be compact and stable.

Further, as shown in fig. 9, the micro-droplet generating apparatus further includes a longitudinal moving mechanism 500, the longitudinal moving mechanism 500 includes a first mounting plate 510, a longitudinal moving driving assembly 520, and a longitudinal sliding assembly 530, the mounting bracket 240 is mounted on the first mounting plate 510 by the longitudinal sliding assembly 530, and the longitudinal moving driving assembly 520 is used for driving the mounting bracket 240 to slide along the longitudinal sliding assembly 530. Under the action of the longitudinal movement driving component 520, the mounting bracket 240 can drive the rotation driving mechanism 200 to move in the longitudinal direction, i.e. the joint 230 on the rotation shaft 220 can move in the longitudinal direction. The micro-pipe 100 on the connector 230 can be driven to synchronously move in the longitudinal direction by controlling the connector 230 to move in the longitudinal direction, and when the first opening of the micro-pipe 100 needs to be inserted below the liquid level of the second liquid, the micro-pipe 100 can be driven to move downwards to a preset height by controlling the longitudinal moving mechanism 500; when the micro-pipe 100 needs to be removed, the micro-pipe 100 can be moved upward by controlling the longitudinal moving mechanism 500. The longitudinal movement mechanism 500 also provides conditions for the automatic loading of the micro-pipe 100 into the fitting 230, and when it is desired to mount the micro-pipe 100 on the fitting 230, the micro-pipe 100 can be placed under the fitting 230 such that the second opening 120 of the micro-pipe 100 is aligned with the fitting 230, the longitudinal movement driving assembly 520 is actuated to move the fitting 230 downward, the fourth opening 232 of the fitting 230 is inserted into the second opening 120 of the micro-pipe 100, and then the fitting 230 is moved upward to be reset. Also, after loading the micro-pipe 100 on the joint 230, the longitudinal movement driving assembly 520 may drive the micro-pipe 100 to move downward such that the first opening 110 is inserted below the liquid surface of the second liquid 610, and perform a reciprocating swing to produce micro-droplets.

Specifically, as shown in fig. 8 and 9, the longitudinal movement driving assembly 520 includes a longitudinal movement driving motor 521, a second lead screw 522 and a second lead screw nut 523, the longitudinal movement driving motor 521 is fixedly mounted on the first mounting plate 510, an output end of the longitudinal movement driving motor is connected to the second lead screw 522, the second lead screw nut 523 is mounted in cooperation with the second lead screw 522, and the mounting bracket 240 is connected to the second lead screw nut 523. The second lead screw nut 523 is matched with the second lead screw 522 to convert the rotational motion output by the longitudinal movement driving motor 521 into a linear motion of the second lead screw nut 523 along the axial direction of the second lead screw 522, so that the mounting bracket 240 can be driven to perform a linear motion, and of course, other forms of linear driving assemblies can be adopted to drive the mounting bracket 240. Such as a rack drive.

Referring to fig. 17, another embodiment of the longitudinal movement driving assembly 520 includes a longitudinal movement gear driving motor 1521 with a power-off brake, a first gear 1522 and a first rack 1523, the longitudinal movement gear driving motor 1521 is fixedly mounted on the mounting bracket 240, an output end of the longitudinal movement driving motor is connected to the first gear 1522, the first rack 1523 is fixed on the first mounting plate 510, and the first rack 1523 is mounted in cooperation with the first gear 1522. The first gear 1522 and the first rack 1523 cooperate to convert the rotational motion output by the longitudinal movement gear driving motor 1521 into a linear motion of the longitudinal movement gear driving motor 1521 and the first gear 1522 along the axial direction of the first rack 1523, so as to drive the mounting bracket 240 to perform a linear motion, and of course, other forms of linear driving assemblies may be adopted to drive the mounting bracket 240.

As shown in fig. 10, 11 and 12, the fluid driving mechanism 300 of the present embodiment includes a syringe 350 and a syringe driving assembly 320, and the liquid inlet and outlet of the syringe 350 communicates with the second opening 120 of the micro-channel 100 through the delivery tube 310. The ram 351 of the syringe 350 slides within the barrel of the syringe 350 under the force of the syringe drive assembly 320, and drives the driving fluid therein through the delivery tube 310 and the connector 230 into the microchannel 100, providing a fluid driving force to the first fluid 130 in the microchannel 100. The fluid driving mechanism provided by the present invention is not limited to the above-described embodiments, and for example, a peristaltic pump, a pressure-driven pump, a pneumatic-driven pump, an electroosmotic-driven pump, or the like may be used.

Further, as shown in fig. 12, the fluid driving mechanism 300 further includes a three-way reversing valve 330 and a fluid reservoir, and the second opening 120 of the micro-pipe 100, the fluid inlet and outlet of the syringe 350 and the fluid outlet of the fluid reservoir are communicated with three ports of the three-way reversing valve 330. The three-way directional valve 330 can control the fluid driving mechanism 300 to realize at least the following two modes: firstly, the liquid inlet and outlet of the syringe 350 are communicated with the second opening 120 of the microchannel 100, and the syringe 350 provides a liquid driving force to the microchannel 100 under the driving of the syringe driving component 320, so as to push the first liquid in the microchannel 100 out of the first opening 110 or suck the first liquid into the microchannel 100 from the first opening 110; secondly, the liquid inlet and outlet of the injector 350 are communicated with the liquid storage tank, and the injector 350 pumps the driving liquid in the liquid storage tank into the tube body of the injector 350 or pushes the driving liquid in the injector 350 into the liquid storage tank under the driving of the injector driving component 320.

Referring to fig. 8, 9 and 11, in order to improve the generation efficiency of micro droplets, as a preferred embodiment, the number of micro-pipes 100, joints 230, delivery pipes 310 and syringes 350 are multiple, the joints 230 are spaced on the rotating shaft 220, the micro-pipes 100 are mounted on one joint 230, two ends of each delivery pipe 310 are respectively communicated with the second opening of one micro-pipe 100 and the first port of the three-way reversing valve 330, the liquid inlet and outlet of each syringe 350 are communicated with the second port of the three-way reversing valve 330, and the liquid outlet of the liquid storage tank is communicated with the third port of the three-way reversing valve 330. The plurality of microchannels 100 can be driven by the injector 350 and the rotating motor 210 to simultaneously perform the operation of generating micro-droplets, and one three-way directional valve 330 can simultaneously control the generation state of micro-droplets of the plurality of microchannels 100.

As a preferred embodiment, a plurality of three-way directional control valves 330 may be provided corresponding to the plurality of microchannels 100, the connectors 230, the delivery pipes 310 and the injectors 350, and the plurality of three-way directional control valves 330 are respectively communicated with the plurality of delivery pipes 310 and the plurality of injectors 350, so that the generation states of the micro droplets in the plurality of microchannels 100 can be independently controlled by independently controlling the plurality of three-way directional control valves.

Further, as shown in fig. 12, 14 and 15, the fluid driving mechanism 300 further includes an installation block 340, the three-way directional valve 330 and the injector 350 are fixedly installed on the installation block 340, a plurality of first flow channels 341, a plurality of second flow channels 342, a third flow channel 343 and a plurality of liquid separating flow channels 344 are formed in the installation block 340, two ends of each first flow channel 341 are respectively communicated with a first interface of the delivery pipe 310 and one three-way directional valve 330, two ends of each second flow channel 342 are respectively communicated with a liquid inlet and outlet of the injector 350 and a second interface of one three-way directional valve 330, the third flow channel 343 is communicated with the liquid storage tank and the plurality of liquid separating flow channels 344, and each liquid separating flow channel 344 is communicated with a third interface of one three-way directional valve 330.

Specifically, as shown in fig. 10, the injector driving assembly 320 includes an injector driving motor 321, a third lead screw 322 and a third lead screw nut 323, wherein an output end of the injector driving motor 321 is connected to the third lead screw 322, the third lead screw nut 323 is installed in cooperation with the third lead screw 322, and the push rods 351 of the plurality of injectors 350 are connected to the third lead screw nut 323 through a connecting member (not shown). The third lead screw nut 323 is matched with the third lead screw 322 to convert the rotational motion output by the injector driving motor 321 into a linear motion of the third lead screw nut 323 along the axial direction of the third lead screw 322, so as to drive the push rod 351 of the injector 350 to perform a linear motion, and of course, other forms of linear driving assemblies may be adopted to drive the push rod 351. Such as a rack drive.

Referring to fig. 16, an alternative syringe driving assembly 320 includes a syringe gear driving motor 1321 with a power-off brake, a second gear 1322 and a second rack 1323, wherein an output end of the syringe driving motor 1321 is connected to the second gear 1322, the second rack 1323 is connected to a second mounting plate 360, the second rack 1323 is mounted to the second gear 1322, and push rods 351 of a plurality of syringes 350 are connected to the syringe gear driving motor 1321 through a connecting member (not shown). The second gear 1322 and the second rack 1323 cooperate to convert the rotational motion output by the syringe driving motor 1321 into a linear motion of the syringe gear driving motor 1321 and the second gear 1322 along the axial direction of the second rack 1323, so as to drive the syringe 350 to perform a linear motion 351, and of course, other forms of linear driving assemblies may be used to drive the push rod 351.

Furthermore, the fluid driving mechanism 300 further comprises a second mounting plate 360, and the mounting block 340 and the syringe driving motor 321 are fixedly mounted on the second mounting plate 360, and the second mounting plate 360 makes the fluid driving mechanism 300 more compact and stable. While the first mounting plate may be combined with the second mounting plate to save space, for example, as shown in fig. 19, the syringe drive assembly 320 may be mounted on an integral mounting plate 1360 without any change in the remaining mounting and driving means.

As a preferred embodiment, the rotating motor 210 may be a galvanometer motor, which can provide stable and high-speed reciprocating rotation and oscillation motion, and the oscillation amplitude and frequency can be set as required, thereby greatly increasing the application range of the micro-droplet generating device of the present invention. Meanwhile, the needle withdrawing plate driving motor 421, the longitudinal movement driving motor 521 and the injector driving motor 321 can adopt stepping motors, and the stepping motors are matched with the screw rod and nut structure to accurately control the stroke of linear motion, so that the automation degree is improved.

Preferably, the rotating motor 210 is a motor with a closed-loop control vibration angle or position, and the motor with the closed-loop control vibration angle or position drives the rotating driving mechanism 200 to perform reciprocating swing, so as to precisely control the swing track of the micro-pipe 100, thereby further reducing the disturbance caused by the environment and the system. Another advantage of this method is that system parameters can be adjusted such that the critical volume is reached within one oscillation period (as indicated by the arrow in fig. 7). This means that only one droplet is generated per cycle of the rotational movement. This allows the change in drop volume due to fluctuations in various environmental factors not to accumulate to the next cycle. Thereby, droplets of uniform size can be generated in large quantities. This is also an advantage not possessed by other published solutions for generating nanoliter/picoliter-sized emulsified droplets by mechanical motion.

The use of a motor with closed-loop control of the vibration angle or position in the present invention is described below in connection with fig. 16. The motor for controlling the vibration angle or position in a closed loop mode comprises an infrared position sensor, a control circuit, a signal processing circuit and the like. In the present invention, an infrared position sensor is installed on the rotating shaft 220 of the rotation driving mechanism 200, the position signal obtained by the infrared position sensor is fed back to the control circuit, the control circuit respectively performs proportional, integral and differential operation processing on the fed-back position signal according to the PID automatic control principle, and the absolute position accurate control during the motor movement is realized by combining the position feedforward with the signal processing circuit of a speed loop, a current loop, etc. The motor for controlling the vibration angle or position in a closed loop mode can avoid the change of the vibration position caused by the change of a complex load environment of other vibration motors, and is beneficial to accurately controlling the volume and the generation speed of liquid drops in engineering.

In this embodiment, a reservoir with a volume of 10 μ L ~ 100 μ L is disposed between the first opening 110 and the second opening 120 of the micro-tube 100, and the reservoir can store a certain amount of the first liquid, so as to ensure that the first liquid is sufficient to generate a required amount of micro-droplets, and at the same time, the reservoir can prevent the first liquid from being sucked into the adapter 230 and the delivery tube 310 through the micro-tube 100, thereby preventing the system from being contaminated by the sample.

Preferably, the microchannel 100 may be made of a non-rigid material and have some flexibility. A certain flexibility refers to the fact that the micro-pipe 100 can have a certain standing wave phenomenon in the moving path of the first opening 110 of the micro-pipe 100 under the driving of the rotary driving mechanism 200. The micro-pipeline made of a certain flexible material is adopted, so that the disturbance on the liquid level is further reduced, the generated liquid drops are easier and more uniform, and the generated liquid crushing phenomenon is further reduced.

In this embodiment, the microchannels 100 are made of a low surface energy polypropylene material; the delivery tube 310 is made of Teflon (Teflon) material.

In an embodiment, the first opening 110 of the microchannel 100 has a nozzle inner diameter of 1 μm to 250 μm, and more preferably, the first opening 110 of the microchannel 100 has a nozzle inner diameter of 10 μm to 100 μm.

Next, the structure of the digital PCR chip and its operation principle will be described in detail with reference to the accompanying drawings and embodiments.

Referring to fig. 21 to 22, there are shown a digital PCR chip, a microchannel 100 (also referred to as an output needle in the present invention) according to the present invention, and a negative pressure device having a negative pressure needle 50 for generating negative pressure.

The digital PCR chip of this embodiment comprises a chip body 10 having a liquid droplet storage chamber 1, a liquid inlet 4 and a liquid outlet 5 provided on the chip body 10, and an accommodation chamber 61 vertically provided on the chip body 10 and communicating with the liquid inlet 4, wherein the chip body 10 further comprises a first channel 2 for communicating the liquid inlet 4 with the liquid droplet storage chamber 1, and a second channel 3 for communicating the liquid outlet 5 with the liquid droplet storage chamber 1, respectively, wherein the first channel 2 has a first internal passage located inside the chip body 10, and the second channel 3 also has a second internal passage located inside the chip body 10.

In the digital PCR chip, the accommodating cavity 61 extends upward from the upper surface of the chip body 10, and the liquid inlet 4 is located at the bottom of the accommodating cavity 61. When the device is used, oil phase is filled in the liquid drop storage cavity 1, the first channel 2, the second channel 3 and the accommodating cavity 61, then water phase is filled in the oil phase of the accommodating cavity 61 by using the output gun needle 40, and the output gun needle 40 is reciprocated while the water phase is filled in the oil phase, so that liquid drops are formed in the accommodating cavity 61. The aqueous phase is generally denser than the oil phase and the droplets formed will settle by their own weight to the bottom of the receiving chamber 61 and subsequently pass through the inlet 4 into the first passage 2 and thence into the droplet storage chamber 1.

Specifically, the length of the accommodating cavity 61 is 20 ~ 1000um, the width is 20 ~ 1000um, and the height is 20 ~ 2000 um.. the accommodating cavity 61 can be fixedly connected to the chip body 10, and can also be integrally formed with the chip body 10. in this embodiment, the upper surface of the chip body 10 has an upward vertically extending liquid inlet flow guide pipe 6, and the cavity of the liquid inlet flow guide pipe 6 constitutes the accommodating cavity 61.

In this digital PCR chip, the second channel 3 is also connected to the droplet storage chamber 1 at the end. Preferably, in the digital PCR chip, the first path 2 is preferably connected to the droplet storage chamber 1 at an end portion thereof, and the first inner path is provided on one side of the droplet storage chamber 1; the second channel 3 is also connected to the droplet storage chamber 1 at its end, and the second inner channel and the first inner channel are separately provided on different sides of the droplet storage chamber 1, so that a negative pressure can be generated via the discharge port by the negative pressure gun needle 50 of the negative pressure device, and the auxiliary droplet gradually enters the droplet storage chamber 1 from the first channel 2.

On this chip body 10, the bottom surfaces of first passageway 2, second passageway 3 and liquid droplet storage chamber 1 preferably set up to be located the same high position, and inlet 4 is higher than first passageway 2 in the height of vertical direction, and the drain port 5 is higher than second passageway 3 in the height of vertical direction. The inner diameter of the inlet 4 is preferably set to 4mm to 8mm, and the height is preferably set to 5mm to 15 mm. The inner diameters of the first channel 2 and the second channel 3 are respectively 4mm-10 mm. The length and width of the liquid drop storage cavity 1 are 2-30mm and the height is 20-2000um respectively.

As shown in fig. 26, the droplet storage chamber 1 has a first communication port 1a communicating with the first channel 2, and a second communication port 1b communicating with the second channel 3, the first communication port 1a and the second communication port 1b being provided on different side portions of the droplet storage chamber 1, preferably with the first communication port 1a being provided opposite to the second communication port 1 b; when the cross section of the droplet storage chamber 1 adopts a polygonal structure, the first communication port 1a and the second communication port 1b are preferably provided on a set of opposite corners of the polygon.

In some embodiments, the droplet storage chamber 1 has at least one arc-shaped chamfer, and the first communication port 1a is disposed at the arc-shaped chamfer, so that the first channel 2 is connected to the first communication port 1a to communicate with the droplet storage chamber 1, which is more favorable for realizing a tiling movement after the droplet enters the droplet storage chamber 1. The liquid droplet storage chamber 1 may be a polygon having a circular inner chamfer or a circle or an ellipse.

When the cross section of the droplet storage chamber 1 is a polygon, the arc-shaped chamfer may be formed at a position where two adjacent sides meet, or the arc-shaped chamfer may be formed by performing a large chamfer treatment on one side, and when the cross section of the droplet storage chamber 1 is other irregular shapes, it is preferable to perform the large chamfer treatment. Preferably, the cross-section of the droplet storage chamber 1 has an angle between at least two adjacent sides, and the first communication port 1a is provided at the angle.

In this embodiment, the cross section of the droplet storage chamber 1 is square, and a set of opposite angles between the first communication port 1a and the second communication port 1b is as shown in fig. 26, and the other inner angles are all arranged by circular arc inner chamfers, which is beneficial to maintaining good stability of the droplets in the droplet storage chamber 1. The side length of the square of the cross section of the liquid drop storage chamber 1 is 5-30mm, and the height of the liquid drop storage chamber 1 is 50-1000 um. When the diameter of the liquid drop is reduced, the side length of the liquid drop storage cavity 1 can be reduced to a smaller size, and the height needs to meet the requirement of spreading the liquid drop on one hand and also needs to take the problem of fully utilizing the formula oil into consideration on the other hand.

Preferably, the first channel 2 and the second channel 3 are partially or entirely curved. In this embodiment, as shown in fig. 26, the first passage 2 includes an inlet section 2a having one end communicating with the inlet 4, and an outlet section 2b extending from the other end of the inlet section 2a in an arc toward the droplet storage chamber 1. The feed liquor section 2a is the straight line and extends the section, it is located the outside of liquid drop storage chamber 1 and is parallel with a limit in 1 chamber of liquid drop storage, the one end of feed liquor section 2a is buckled and is extended the play liquid section 2b that forms the arc and extend the section towards the direction in liquid drop storage chamber 1, go out the end connection of liquid section 2a of keeping away from of liquid section 2b and on first intercommunication mouth 1a and with liquid drop storage chamber 1 switch-on, this design does benefit to the liquid drop and gets into under the effect of gravity steadily under the first passageway 2 back via inlet 4 gets into in liquid drop storage chamber 1.

The second channel 3 is arranged centrosymmetrically to the first channel 2. Specifically, second passageway 3 includes the flowing back section 3a that one end is linked together with discharge opening 5 and is the inlet liquid section 3b that the camber line bending extends from the other end of flowing back section 3a towards liquid drop storage chamber 1, and this inlet liquid section 3b is the arc of keeping away from flowing back section 3a and arching gradually, and the end connection of inlet liquid section 3b is on second intercommunication mouth 1b and with liquid drop storage chamber 1 switch-on.

The first channel 2, the droplet storage chamber 1, and the second channel 3 constitute a centrosymmetric structure as a whole. The structural design realizes the stable conveying of the liquid drops and ensures the stability of the liquid drops.

The chip body 10 is mainly formed by stacking a chip cover plate and a chip substrate along the thickness direction, the chip cover plate is a flat plate, a groove is formed in the chip substrate, and the flat plate and the groove are stacked and compressed to form a liquid drop storage cavity 1, a first channel 2 and a second channel 3. In this embodiment, the opening of the groove is downward, the chip substrate 101 is located above the chip cover plate 102, and the chip cover plate 102 is a transparent glass plate, a transparent PC plate, a transparent acrylic plate, a COP transparent plate, or a black non-reflective plate made of non-reflective materials such as POM and PP. The chip substrate 101 and the chip cover plate 102 may be bonded to each other by gluing or ultrasonic or thermocompression bonding, and the edge between the two is required to maintain absolute sealing.

In another embodiment as shown in fig. 28 to fig. 36, the opening of the groove is upward, the chip substrate 104 is located below the chip cover plate 103, specifically, the liquid inlet 4 and the liquid outlet 5 are both opened on the chip cover plate 103, and the liquid inlet flow guide tube 6 and the liquid outlet flow guide tube 7 are also integrally formed on the chip cover plate 103; the droplet storage chamber 1, the first channel 2, and the second channel 3 are disposed on the chip substrate 104. The chip cover plate 103 and the chip substrate 104 are both made of plastic, and are welded to the seal by a thermocompression bonding process.

Referring to fig. 21, 22, 23 and 24, the upper surface of the chip body 10, that is, the upper surface of the chip substrate 101, further has a liquid drainage tube 7 extending vertically upward and communicating with the liquid drainage port 5, the liquid drainage tube 7 is mainly used as a negative pressure connector coupled to a negative pressure gun pin 50, and the negative pressure gun pin 50 is coupled to the liquid drainage tube 7 to form negative pressure to the droplet storage chamber 1. In this embodiment, the liquid inlet flow guide tube 6 and the liquid outlet flow guide tube 7 are integrally formed on the chip substrate 101, but in other embodiments, they may also be formed first by independent processing and then connected to the chip substrate 101 by ultrasonic welding or glue bonding. The pipe orifice of each liquid inlet guide pipe 6 can be sealed by a sealing cover 201 which is detachably connected, so that the accommodating cavity 61 is sealed; the opening of the liquid discharge guide tube 7 can be sealed by a sealing film 30.

Referring to fig. 21 to 26, in the chip body 10, the droplet storage chamber 1, the first channel 2 and the second channel 3 together form a chip unit, and the chip body 10 is provided with a plurality of chip units arranged at intervals along the length direction, so that a plurality of groups of sample loading and analysis detection can be performed simultaneously. Correspondingly, there are also a plurality of liquid inlet 4, liquid outlet 5 and accommodating cavity 61, and a plurality of liquid inlet guide pipe 6 and liquid outlet guide pipe 7. For the convenience of manufacture and operation, all the sealing covers 201 matched with the plurality of liquid inlet guide pipes 6 are integrally arranged to form an integral sealing cover component 20, and the sealing film 30 also serves as an integral component and can simultaneously serve as the sealing of the pipe orifices of all the liquid outlet guide pipes 7.

The invention also provides a detection method adopting the digital PCR chip or the digital PCR detection system, which comprises a sample loading step of conveying liquid drops to the liquid drop storage cavity 1, wherein the sample loading step comprises the following steps:

filling oil phase into a liquid drop storage cavity 1, a first channel 2, a second channel 3 and an accommodating cavity 61 of the digital PCR chip;

injecting water phase into the oil phase in the accommodating cavity 61 by using the micro-pipe 100 (namely the output gun needle 40), and enabling the micro-pipe 100 to swing back and forth while injecting, so that liquid drops are formed in the accommodating cavity 61;

the droplets are transported through the inlet port 4, the first channel 2, and to the droplet storage chamber 1.

Wherein the droplet storage chamber 1, the first passage 2, and the second passage 3 are preferably filled with an oil phase before the water phase is injected. Before injecting the water phase, preferably keeping the liquid inlet 4 and the liquid outlet 5 in a sealed state, and horizontally standing the PCR chip for more than 5 min; after the formation of the liquid droplets is started or after the generation of the liquid droplets is completed, the negative pressure means is turned on, the discharge of the oil phase from the liquid discharge port 5 is promoted and the flow of the liquid droplets to the liquid droplet storage chamber 1 is promoted.

The specific detection process is carried out according to the following steps: oil phase is filled in the liquid drop storage cavity 1, the first channel 2, the second channel 3 and the containing cavity 61 of the chip body 10 in advance, and the pipe openings of the liquid inlet guide pipe 6 and the liquid discharge guide pipe 7 are sealed by the sealing cover 201 and the sealing film 30 respectively. After the chip body 10 stands still for more than 5min, the sealing cover 201 is opened, the output needle of the output gun needle 40 of the liquid drop generating device is inserted into the accommodating cavity 61 of the liquid inlet flow guide pipe 6, so that the port of the output needle (i.e. the first opening 110 of the micro-pipe 100) is positioned below the liquid level of the oil phase to inject water and the output needle reciprocates while injecting water, and liquid drops are formed in the accommodating cavity 61. The produced liquid drops are accumulated at the bottom of the accommodating cavity 61 under the action of self gravity, and partial liquid drops naturally fall to the first pipeline 2 through the liquid inlet 4, at the moment, the liquid level of the oil phase is increased in the liquid inlet 4 due to the intervention of the liquid drops, but the stability of liquid drop generation is not influenced. After the liquid drops are generated, the sealing film 30 at the pipe orifice of the liquid drainage and guide pipe 7 is punctured (puncturing can be performed by additionally arranging an actuating mechanism matched with an instrument), negative pressure is slowly generated by a negative pressure gun needle 50 connected with a negative pressure device, the liquid drops slowly pass through the first channel 2 from the liquid inlet 4 along with the pressure action and enter the liquid drop storage cavity 1, and are tiled to the liquid drop storage area 1 in a fan-shaped area, as shown in fig. 37 to 39, at the moment, the liquid drop generation and the primary tiling process are completed, and the chip body 10 can be compressed through a mechanical structure.

The process of compressing tightly can compress tightly or several fixed points compress tightly at whole chip body 10 upper surface to buffer pressure through structures such as spring, if adopt several fixed points to compress tightly then need avoid excitation light irradiation or camera to detect light path region, thereby can carry out real-time fluorescence and read, observe the motion state of liquid drop at any time.

Furthermore, by adjusting the thickness and area of the droplet storage chamber 1, the volume of the droplet, and the total volume of the sample, it is possible to realize tiling of one precise layer, or two layers as shown in FIG. 41, or three or more layers as shown in FIG. 42. assuming a sample volume of 20 microliters, a droplet volume of 1 nanoliter, a chip area of 16mm by 16mm, and a chip thickness of 125 ~ 150 micrometers, 2 ten thousand droplets generated can only be tiled in one layer, whereas a sample volume of 20 microliters, a droplet volume of 1 nanoliter, if the chip area is adjusted to 11.5mm by 11.5mm, and the thickness is adjusted to 200 ~ 275 micrometers, 2 ten thousand droplets can only be tiled in 2 layers.

The tiling mode of the multilayer liquid drops can realize the multilayer observation of the liquid drops with higher flux in unit area. The method is of great importance for improving the overall detection flux of the digital PCR equipment for detecting liquid drops in an image mode, and the bottleneck problem of low detection flux of the equipment is solved.

The above-mentioned embodiments are merely illustrative of the technical idea and features of the present invention, and the purpose thereof is to enable those skilled in the art to understand the contents of the present invention and implement the present invention, and not to limit the scope of the present invention, and all equivalent changes or modifications made according to the spirit of the present invention should be covered in the scope of the present invention.

Claims

1. A digital PCR chip, including the chip body with liquid drop storage chamber and setting up the inlet on the chip body, characterized by: the digital PCR chip also comprises an accommodating cavity which is vertically arranged on the chip body and is communicated with the liquid inlet, and a liquid outlet which is arranged on the chip body; the chip body further comprises a first channel and a second channel, the first channel is used for communicating the liquid inlet with the liquid drop storage cavity, the second channel is used for communicating the liquid discharge port with the liquid drop storage cavity, the first channel is provided with a first inner channel located inside the chip body, and the second channel is provided with a second inner channel located inside the chip body.

2. The digital PCR chip of claim 1, wherein: the holding cavity extends upwards from the upper surface of the chip body, and the liquid inlet is positioned at the bottom of the holding cavity.

3. The digital PCR chip of claim 1, wherein the receiving chamber has a length of 2 ~ 30mm, a width of 2 ~ 30mm, and a height of 20 ~ 2000 um.

4. The digital PCR chip of claim 1, wherein: the holding cavity and the chip body are integrally formed, or the holding cavity and the chip body are fixedly connected.

5. The digital PCR chip of claim 1, wherein: the first channel communicates at an end with the droplet storage chamber; and/or the second channel communicates at an end with the droplet storage chamber.

6. The digital PCR chip of claim 1, wherein: the first channel is located on one side of the droplet storage chamber; and/or the second channel is located to one side of the droplet storage chamber.

7. The digital PCR chip of claim 1, wherein: the first inner passage and the second inner passage are respectively arranged at two different sides of the liquid drop storage cavity.

8. The digital PCR chip of claim 1, wherein: the droplet storage chamber has a first communicating port communicating with the first passage, and a second communicating port communicating with the second passage, and the first communicating port and the second communicating port are provided on two opposite side portions of the droplet storage chamber.

9. The digital PCR chip of claim 8, wherein: the first communication port is arranged right opposite to the second communication port.

10. The digital PCR chip of claim 8, wherein: the liquid drop storage cavity is provided with at least one arc-shaped chamfer, and the first communication port is arranged at the arc-shaped chamfer.

11. The digital PCR chip of claim 8, wherein: the liquid drop storage cavity is a polygon with an arc inner chamfer; alternatively, the droplet storage chamber is circular or elliptical.

12. The digital PCR chip of claim 8, wherein: the liquid drop storage cavity is square or rectangular, the first communication port and the second communication port are respectively arranged on opposite corners of the liquid drop storage cavity, the first inner passage and the second inner passage are respectively arranged on two opposite sides of the liquid drop storage cavity, and the first inner passage and the second inner passage are respectively communicated with the first communication port and the second communication port at the end parts.

13. The digital PCR chip of claim 1, wherein: the first channel and the second channel are partially or wholly curved.

14. The digital PCR chip of claim 13, wherein: the first channel comprises at least one straight extension section and at least one arc extension section, one end of the straight extension section is communicated with the liquid inlet, and the inner space of the at least one straight extension section and the inner space of the at least one arc extension section form the first inner passage.

15. The digital PCR chip of claim 14, wherein: the first inner passage is composed of an inner space of a straight extension section and an arc extension section, the straight extension section is located on the outer side of the liquid drop storage cavity and is parallel to one side of the liquid drop storage cavity, one end of the straight extension section bends towards the direction of the liquid drop storage cavity and extends to form the arc extension section, and the end part, far away from the straight extension section, of the arc extension section is communicated with the liquid drop storage cavity.

16. The digital PCR chip of claim 1, 13, 14 or 15, wherein: the droplet storage chamber, the first channel, and the second channel form a centrosymmetric structure.

17. The digital PCR chip of claim 1, wherein: the first channel, the second channel and the bottom surface of the liquid drop storage chamber are located at the same height position.

18. The digital PCR chip of claim 1, wherein: the liquid inlet is higher than the first channel in the vertical direction, and/or the liquid outlet is higher than the second channel in the vertical direction.

19. The digital PCR chip of claim 1, wherein the loading port has an inner diameter of 4mm to 10mm and a height of 5mm to 15mm, and/or the droplet storage chamber has a length and a width of 2 mm to 30mm and a height of 20 um to 1000um, respectively, and/or the chip body has a thickness of 1 ~ 6 mm.

20. The digital PCR chip of claim 1, wherein: the chip also comprises a sealing cover used for sealing the accommodating cavity.

21. The digital PCR chip of claim 20, wherein: the accommodating cavity is provided with a plurality of accommodating cavities, correspondingly, the sealing covers are also provided with a plurality of accommodating cavities, and all the sealing covers are integrally arranged on one integral component.

22. The digital PCR chip of claim 1, wherein: the digital PCR chip also comprises a liquid discharge pipe vertically arranged on the chip body, and the liquid discharge pipe is communicated with the liquid discharge port.

23. The digital PCR chip of claim 22, wherein: the drain pipe extends upwards from the upper surface of the chip body and is integrally formed or fixedly connected with the chip body.

24. The digital PCR chip of claim 1, wherein: and a negative pressure joint which is used for being matched and connected with the outlet of the negative pressure device is arranged on the liquid outlet.

25. The digital PCR chip of claim 1, wherein: the chip body is formed by overlapping a chip cover plate and a chip substrate along the thickness direction, the chip cover plate is a flat plate, a groove is formed in the chip substrate, and the flat plate and the groove are overlapped and compressed mutually to form the liquid drop storage cavity, the first channel and the second channel.

26. The digital PCR chip of claim 25, wherein: the groove is opened downwards, the chip substrate is positioned above the chip cover plate, and the chip cover plate is a transparent glass plate, a transparent PC plate, a transparent acrylic plate, a COP transparent plate or a black non-reflecting plate.

27. The digital PCR chip of claim 25, wherein: the groove opening faces upwards, the chip substrate is located below the chip cover plate, and the chip substrate and the chip cover plate are made of plastics respectively.

28. The digital PCR chip of claim 1, wherein: the liquid drop storage cavity, the first channel and the second channel jointly form a chip unit, and the chip body is provided with a plurality of chip units.

29. The digital PCR chip of claim 28, wherein: the chip body is long, and the plurality of chip units are distributed along the length direction of the chip body.

30. A digital PCR detection system comprising a digital PCR detection device, further comprising a digital PCR chip as claimed in any one of claims 1 to 29, and a negative pressure device cooperating with the digital PCR chip for generating a negative pressure in the first channel, the droplet storage chamber and the second channel.

31. A digital PCR detection method based on the digital PCR chip of any one of claims 1 to 29 or the digital PCR detection system of claim 30, wherein the detection method comprises a loading step of delivering droplets to the droplet storage chamber, the loading step comprising:

32. The digital PCR detection method of claim 31, wherein: before injecting the aqueous phase, the droplet storage chamber, the first channel, and the second channel are filled with an oil phase.

33. The digital PCR detection method of claim 31, wherein: after the oil phase is filled and before the water phase is injected, the liquid inlet and the liquid outlet are kept in a sealed state, and the PCR chip is horizontally kept standing for more than 5 min.

34. The digital PCR detection method of claim 31, wherein: after the formation of the liquid droplets is started or after the generation of the liquid droplets is completed, the negative pressure device is turned on to promote the discharge of the oil phase from the liquid discharge port and the flow of the liquid droplets to the liquid droplet storage chamber.