阅读说明：本技术 可切换的温育模块、pcr扩增检测仪 (Switchable incubation module and PCR amplification detector ) 是由 林佳慧 黄维雷 颜金鹏 于 2021-10-09 设计创作，主要内容包括：本发明涉及一种可切换的温育模块,包括用于加温微流控芯片的温育本体,温育本体包括：若干加热模块,用于加热微流控芯片上的反应腔；其中,至少有两加热模块上的加热温度不同；旋转驱动结构,用以驱使微流控芯片与加热模块相对转动；每一加热模块上均设置有相同数量的加热区,若干加热模块上的加热区与微流控芯片同心设置；开启温育时,在旋转驱动结构的驱使下,微流控芯片在不同加热温度的加热模块的加热区依序转动,以切换微流控芯片的反应腔在温育时的加热温度。本发明还涉及一种PCR扩增检测仪。通过可切换的温育模块,以快捷提供微流控芯片上的反应腔扩增反应所需温度。(The invention relates to a switchable incubation module comprising an incubation body for warming a microfluidic chip, the incubation body comprising: the heating modules are used for heating the reaction cavity on the microfluidic chip; wherein, the heating temperatures of at least two heating modules are different; the rotation driving structure is used for driving the micro-fluidic chip and the heating module to rotate relatively; each heating module is provided with the same number of heating zones, and the heating zones on the plurality of heating modules are concentrically arranged with the microfluidic chip; when the incubation is started, the microfluidic chip rotates in sequence in the heating zones of the heating modules with different heating temperatures under the driving of the rotary driving structure so as to switch the heating temperatures of the reaction cavity of the microfluidic chip during the incubation. The invention also relates to a PCR amplification detector. The temperature required by the amplification reaction of the reaction cavity on the microfluidic chip can be quickly provided by the switchable incubation module.)

1. A switchable incubation module comprising an incubation body for warming a microfluidic chip, characterized in that the incubation body comprises:

the heating modules are used for heating the reaction cavity on the microfluidic chip; wherein, the heating temperatures of at least two heating modules are different;

the rotation driving structure is used for driving the micro-fluidic chip and the heating module to rotate relatively;

the heating modules are provided with the same number of heating zones, and the heating zones on the heating modules are concentrically arranged with the microfluidic chip; when the incubation is started, the microfluidic chip sequentially rotates in the heating areas of the heating modules with different heating temperatures under the driving of the rotary driving structure so as to switch the heating temperature of the reaction cavity of the microfluidic chip during the incubation.

2. The switchable incubation module of claim 1, further comprising an insulation layer to maintain temperature within the incubation body.

3. The switchable incubation module of claim 1, wherein the heating zones on a number of the heating modules are equidistant from the central axis of the heating modules.

4. The switchable incubation module of claim 1, wherein the heating zones of different heating modules are spaced from the central axis of the heating module by different distances, such that after the microfluidic chip and the heating module are driven to rotate relative to each other, the reaction solution to be heated on the microfluidic chip moves under the centrifugal force to contact the heating modules with different heating temperatures.

5. The switchable incubation module of claim 3 or 4, further comprising a motion movement mechanism connected to the heating module, wherein the motion movement mechanism is controlled to alternately control different heating modules to contact the reaction chamber on the microfluidic chip.

6. The switchable incubation module of claim 5, wherein there is a gap between adjacent heating zones of several of the heating modules, wherein a heating zone on one heating module passes through a gap between heating zones of another heating module to contact a reaction chamber on a microfluidic chip.

7. The switchable incubation module of claim 1 or 6, wherein at least one of the heating modules comprises a first heating body, a first temperature controlled heating plate, and a first thermally insulating fixture block, the first heating body and the first temperature controlled heating plate being fixed by the first thermally insulating fixture block; the first heating body extends to a plurality of first extension columns along the outer contour of the first heating body in the direction close to the central axis of the first heating body, the first extension columns are further provided with first heating columns at the side close to the microfluidic chip, and the first heating columns are controlled to move to a reaction cavity on the microfluidic chip so as to provide proper reaction temperature.

8. The switchable incubation module of claim 1, wherein the rotational drive structure is configured to drive rotation of the microfluidic chip.

9. The switchable incubation module of claim 1, wherein the rotary drive mechanism is configured to drive rotation of a number of the heating modules.

10. A PCR amplification detection apparatus, comprising a reaction module, a switchable incubation module according to any one of claims 1-9, and a fluorescence detection module arranged in sequence from top to bottom.

[ technical field ] A method for producing a semiconductor device

The invention relates to the technical field of fluorescence detection, in particular to a switchable incubation module and a PCR amplification detector.

[ background of the invention ]

The substance for nucleic acid detection is a nucleic acid of a virus. The nucleic acid detection is to find out whether the respiratory tract specimen, blood or feces of the patient have the nucleic acid of the virus invaded from the outside to determine whether the patient is infected by the virus. Thus, once a nucleic acid positive test is made, the presence of a virus in the patient is demonstrated. All organisms contain nucleic acids, including deoxyribonucleic acid (DNA) and ribonucleic acid (RNA), and in the case of the novel coronaviruses, a virus containing only RNA, the specific RNA sequence in the virus being a marker to distinguish the virus from other pathogens. In clinical laboratory tests, if a nucleic acid sequence specific for a novel coronavirus can be detected in a patient sample, it is suggested that the patient may be infected with the novel coronavirus.

The most common method for detecting virus-specific sequences is fluorescent quantitative PCR (polymerase chain reaction). The method is a method for measuring the total amount of products after each polymerase chain reaction cycle by using fluorescent chemical substances in DNA amplification reaction, and is a method for quantitatively analyzing a specific DNA sequence in a sample to be detected by an internal reference method or an external reference method. The fluorescent quantitative PCR instrument can monitor that the cycle number (Ct value) of fluorescence reaching a preset threshold value is related to the concentration of the virus nucleic acid, and the Ct value is smaller when the concentration of the virus nucleic acid is higher.

The traditional nucleic acid detection process has more processing steps and long time consumption (in the traditional PCR amplification step, a single temperature control chamber is used for heating and cooling, a heating sheet is used for controlling the temperature change of a PCR reaction cavity,

it is comparatively easy to control temperature control chip intensification, but its cooling only can rely on natural convection, leads to spending the longer time just can reach the temperature conversion, and the heating plate cost is higher and fragile, and PCR sensitivity demand is higher in addition, receives environmental disturbance easily, and traditional nucleic acid detects needs 3 each negative pressure rooms at least, is equipped with extra equipment such as professional and centrifuge simultaneously, and the construction cost is high, and the following hospital of second grade is difficult independently to develop, presents the centralized distribution situation.

Accordingly, there is a need for improvements in the art that overcome the deficiencies in the prior art.

[ summary of the invention ]

In view of the deficiencies of the prior art, it is an object of the present invention to provide a switchable incubation module comprising an incubation body for warming a microfluidic chip, the incubation body comprising:

the heating modules are used for heating the reaction cavity on the microfluidic chip; wherein, the heating temperatures of at least two heating modules are different;

the rotation driving structure is used for driving the micro-fluidic chip and the heating module to rotate relatively;

the heating modules are provided with the same number of heating zones, and the heating zones on the heating modules are concentrically arranged with the microfluidic chip; when the incubation is started, the microfluidic chip sequentially rotates in the heating areas of the heating modules with different heating temperatures under the driving of the rotary driving structure so as to switch the heating temperature of the reaction cavity of the microfluidic chip during the incubation.

Preferably, the incubator further comprises an insulating layer for maintaining the temperature in the incubation body.

Preferably, the heating zones on the plurality of heating modules are equidistant from a central axis of the heating modules.

Preferably, the distances between the heating zones on different heating modules and the central shaft of the heating module are different, so that after the microfluidic chip and the heating module are driven to rotate relatively, the reaction liquid to be heated on the microfluidic chip moves under the action of centrifugal force to contact the heating modules with different heating temperatures.

Preferably, the device further comprises a movement moving mechanism, the movement moving mechanism is connected with the heating modules, and the movement moving mechanism is controlled to alternately control different heating modules to be in contact with reaction cavities on the microfluidic chip.

Preferably, gaps exist between adjacent heating zones of a plurality of heating modules, wherein the heating zone on one heating module passes through the gap between the heating zones of another heating module to contact the reaction cavity on the microfluidic chip.

Preferably, at least one of the heating modules comprises a first heating body, a first temperature control heating plate and a first heat insulation fixing block, and the first heating body and the first temperature control heating plate are fixed through the first heat insulation fixing block; the first heating body extends to a plurality of first extension columns along the outer contour of the first heating body in the direction close to the central axis of the first heating body, the first extension columns are further provided with first heating columns at the side close to the microfluidic chip, and the first heating columns are controlled to move to a reaction cavity on the microfluidic chip so as to provide proper reaction temperature.

Preferably, the rotation driving structure is used for driving the micro-fluidic chip to rotate.

Preferably, the rotary driving mechanism is used for driving a plurality of heating modules to rotate.

The invention also relates to a PCR amplification detector which is characterized by comprising a reaction module, the switchable incubation module and a fluorescence detection module which are sequentially arranged from top to bottom.

Compared with the prior art, the invention has the beneficial effects that:

the invention relates to a switchable incubation module comprising an incubation body for warming a microfluidic chip, the incubation body comprising: the heating modules are used for heating the reaction cavity on the microfluidic chip; wherein, the heating temperatures of at least two heating modules are different; the rotation driving structure is used for driving the micro-fluidic chip and the heating module to rotate relatively; each heating module is provided with the same number of heating zones, and the heating zones on the plurality of heating modules are concentrically arranged with the microfluidic chip; when the incubation is started, the microfluidic chip rotates in sequence in the heating zones of the heating modules with different heating temperatures under the driving of the rotary driving structure so as to switch the heating temperatures of the reaction cavity of the microfluidic chip during the incubation. The invention also relates to a PCR amplification detector. The temperature required by the amplification reaction of the reaction cavity on the microfluidic chip can be quickly provided by the switchable incubation module.

The foregoing description is only an overview of the technical solutions of the present invention, and in order to make the technical solutions of the present invention more clearly understood and to implement them in accordance with the contents of the description, the following detailed description is given with reference to the preferred embodiments of the present invention and the accompanying drawings. The detailed description of the present invention is given in detail by the following examples and the accompanying drawings.

[ description of the drawings ]

The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this application, illustrate embodiment(s) of the invention and together with the description serve to explain the invention without limiting the invention. In the drawings:

FIG. 1 is a schematic diagram of the structure of an incubation module of the present invention;

FIG. 2 is a schematic structural view of several heating modules of the present invention;

FIG. 3 is a schematic structural diagram of the moving mechanism of the present invention;

FIG. 4 is a schematic view of a different heating body of the present invention;

FIG. 5 is a schematic diagram of a second heating module of the present invention;

FIG. 6 is a schematic diagram of a third heating module of the present invention;

FIG. 7 is a schematic view of a first heating module of the present invention;

FIG. 8 is a schematic structural diagram of a rotary driving structure according to the present invention;

FIG. 9 is a schematic structural diagram of a fluorescence detection module according to the present invention.

Description of reference numerals:

100. a detector;

101. a moving mechanism; 1011. a support; 1012. a circular shaft; 1013. a micro push rod; 1014. a vertical plate; 1021. a third fixing plate; 1022. a second fixing plate; 1023. a first fixing plate; 1024. a guide bar; 1025. a temperature control module fixing plate; 1026. a bearing;

102. an incubation module; 110. a first heating module; 111. a first extended column; 112. a first heating column; 113. a first temperature controlled heating plate; 114. a first heat insulation fixed block; 115. a first heating body;

120. a second heating module; 121. a heat-conducting column; 122. a second temperature controlled heating plate; 123. fixing a column; 124. a second heating body;

130. a third heating module; 131. a second extended column; 132. a second heating column; 133. a third temperature control heating plate; 134. a third heat insulation fixed block; 135. a third heating body;

103. a rotation driving structure; 1031. a servo motor; 1032. a servo motor vertical plate; 1033. a servo motor fixing plate; 1034. a chip fixing support; 1035. a microfluidic chip;

104. a fluorescence detection module; 1041. a light splitting sheet; 1042. a light emitter; 1043. an imaging detector.

[ detailed description ] embodiments

The foregoing and other objects, features, aspects and advantages of the present invention will become more apparent from the following detailed description of the present invention when taken in conjunction with the accompanying drawings, which will enable those skilled in the art to practice the present invention with reference to the accompanying specification. In the drawings, the shape and size may be exaggerated for clarity, and the same reference numerals will be used throughout the drawings to designate the same or similar components. In the following description, terms such as center, thickness, height, length, front, back, rear, left, right, top, bottom, upper, lower, and the like are used based on the orientation or positional relationship shown in the drawings. In particular, "height" corresponds to the dimension from top to bottom, "width" corresponds to the dimension from left to right, and "depth" corresponds to the dimension from front to back. These relative terms are for convenience of description and are not generally intended to require a particular orientation. Terms concerning attachments, coupling and the like (e.g., "connected" and "attached") refer to a relationship wherein structures are secured or attached, either directly or indirectly, to one another through intervening structures, as well as both movable or rigid attachments or relationships, unless expressly described otherwise.

The present invention will be further described with reference to the accompanying drawings and the detailed description, and it should be noted that any combination of the embodiments or technical features described below can be used to form a new embodiment without conflict. It will be understood that terms such as "having," "including," and "comprising," as used herein, do not preclude the presence or addition of one or more other elements or groups thereof.

Example one

As shown in fig. 1-9, the present invention relates to a switchable incubation module 102 comprising an incubation body for warming a microfluidic chip, the incubation body comprising:

the heating modules are used for heating the reaction cavity on the microfluidic chip; wherein, the heating temperatures of at least two heating modules are different;

the rotation driving structure 103 is used for driving the micro-fluidic chip and the heating module to rotate relatively;

each heating module is provided with the same number of heating zones (in some embodiments, the heating zones are convex heating zones on the heating modules), and the heating zones on the plurality of heating modules are concentrically arranged with the microfluidic chip; when the incubation is started, the microfluidic chip rotates in sequence in the heating zones of the heating modules with different heating temperatures under the driving of the rotary driving structure so as to switch the heating temperatures of the reaction cavity of the microfluidic chip during the incubation. The number of the heating modules is related to the number of different temperature values required by the reaction of the microfluidic chip. When the microfluidic chip is used in a PCR amplification reaction, three different temperatures are generally required to be set, in this case, the incubation module 102 includes three heating modules, as shown in fig. 2 and 4, in this case, the incubation module 102 includes a plurality of temperature-changing regions, each temperature-changing region includes a heating region on each heating module, for example, a temperature-changing region includes a heating region on the first heating module 110, a heating region on the second heating module 130, and a heating region on the third heating module 120.

It should be understood that the incubation body is an incubation device commonly used in the heating process of the microfluidic chip, and is generally a sealing structure and the like.

In some embodiments, the heating module further comprises a heating body, which may be configured in any shape, only by ensuring that the heating region on the heating body can heat the reaction chamber on the microfluidic chip. It should be understood that the microfluidic chip may be provided in any shape. Preferably, the heating body is arranged in a ring shape, and in this case, the microfluidic chip can also be arranged in a disk shape, and the two cooperate to ensure that the heating region can be in sufficient contact with the reaction chamber.

In some embodiments, further comprising an insulating layer to maintain the temperature within the incubation body; preferably, the heat-insulating layer is arranged around the periphery of the microfluidic chip to provide a better heat-insulating environment for the microfluidic chip.

In some embodiments, the heating zones on the plurality of heating modules are equidistant from a central axis of the heating modules. That is, as shown in fig. 2, several heating modules are located on the same circumference, and at this time, as the microfluidic chip rotates, the heating regions on different heating modules may contact the reaction chamber on the microfluidic chip to provide different heating temperatures.

In some embodiments, the heating zones on different heating modules have different distances from the central axis of the heating module, that is, different heating modules are not located on the same circumference, and after the microfluidic chip and the heating module are driven to rotate relatively, the reaction solution to be heated on the microfluidic chip moves under the action of centrifugal force to contact the heating modules with different heating temperatures; for example, in a specific embodiment, the heating zones on different heating modules are located at different positions of the same radius, and the temperatures of the heating zones on different heating modules are set according to the reaction requirement; after the micro-fluidic chip relatively rotates, the liquid to be heated in the micro-fluidic chip moves away from the center of the micro-fluidic chip under the action of centrifugal force, and sequentially contacts different heating modules in the moving process to realize heating at different temperatures.

When the micro-fluidic chip and the heating module are driven to rotate relatively, in some embodiments, the rotation driving structure is used to drive the micro-fluidic chip to rotate, and at this time, the rotation driving structure may be a turntable, and the turntable drives the micro-fluidic chip to rotate. In other embodiments, the rotary driving mechanism is used for driving a plurality of heating modules to rotate; in this case, the rotary drive mechanism acts directly on the different heating modules.

In some embodiments, the device further comprises a moving mechanism 101, wherein the moving mechanism is connected with the heating modules, and the moving mechanism is controlled to alternately control different heating modules to be in contact with the reaction chambers on the microfluidic chip. In some embodiments, the motion moving mechanism 101 includes: the heating device comprises a fixed plate, a guide rod and a push rod, wherein one end of the guide rod is connected with the fixed plate, and the other end of the guide rod is connected with a heating module; the push rod pushes the fixing plate to move so as to drive the heating module to move towards the reaction cavity on the microfluidic chip. Specifically, the first heating module 110, the second heating module 120, and the third heating module 130 are fixed to the first fixing plate 1023, the second fixing plate 1022, and the third fixing plate 1021 respectively by guide rods 1024, and the movement control in the height direction can be realized by three independently operating push rods such as micro push rods at the linear bearing 1026). As shown in fig. 1-4, the device is composed of a bracket 1011, a circular shaft 1012, micro-pushrods 1013 and risers 1014, wherein two brackets 1011 fixed on two risers are used for fixing the circular shaft 1012, and three micro-pushrods 1013 are fixed on the circular shaft 12, so that the control of different directions (three-dimensional directions) can be independently realized.

Furthermore, gaps exist between adjacent heating zones of the heating modules, wherein the heating zone on one heating module passes through the gap between the heating zones of the other heating module to contact the reaction cavity on the microfluidic chip. That is, if the first heating module 110 is the heating module closest to the microfluidic chip, the heat-conducting pillars on the second heating module 120 pass through the gaps between the first heating pillars on the first heating module and the gaps between the second heating pillars on the third heating module to be close to the microfluidic chip; similarly, the second heating pillars 132 of the third heating module 130 pass through the gaps between the pairs of heating pillars of the first heating module 110 to be adjacent to the microfluidic chip.

In some embodiments, when the heating body of the heating module is arranged in a ring shape, and three heating modules are included, as shown in fig. 4 to 7, it may specifically include: the first heating module 110, the second heating module 120 and the third heating module 130, wherein the three heating modules may be disposed below the microfluidic chip or above the microfluidic chip simultaneously, for example, when the three heating modules are disposed below the microfluidic chip, as shown in fig. 4, the first heating module 110, the second heating module 120 and the third heating module 130 are mounted below the microfluidic chip one by one from top to bottom; or are respectively arranged at the upper side and the lower side of the microfluidic chip. When the three heating modules are located on the same side of the microfluidic chip, the three heating modules have different diameters, that is, the first heating module 110, the second heating module 120, and the third heating module 130 are sleeved with each other and have the same circle center, so as to ensure that they do not interfere with each other in the movement process. When the three heating modules are positioned on different sides of the microfluidic chip, the calibers of the heating modules positioned on the same side are ensured not to interfere with each other. It should be understood that when the heating body is annular, the heating module can heat all the reaction chambers on the microfluidic chip at one time, which is quick and time-saving. When the heating module is not annular and three heating modules are arranged, the heating module can be set to be in any shape, in some embodiments, the heating module is different from the microfluidic chip in shape, but the heating module can be fully contacted with the reaction cavity on the microfluidic chip. In other embodiments, a heating module corresponds to only a portion of the area on the microfluidic chip, for example, if the microfluidic chip includes N (N may be any positive integer) reaction chambers, i.e., 16 fluxes, a heating module corresponds to one or more reaction chambers on the microfluidic chip; at this moment, only need guarantee a plurality of heating module dislocation arrange can, the purpose that the dislocation was arranged is in order to guarantee that these three heating module can not interfere with each other when moving along PCR amplification analysis appearance direction of height. When three heating modules are included, the three heating modules are arranged in a staggered manner. It should be noted that if the heating modules are rotatable, the target heating module can be rotated to the position without interference first and then moved along the height direction of the PCR amplification analyzer without limiting the staggered distribution of the three heating modules; at the moment, the heating module only heats part of the reaction cavities at one time, but along with the relative movement of the microfluidic chip and the heating module, the heating module can finish heating all the reaction cavities on the microfluidic chip.

In some embodiments, as shown in fig. 7, the first heating module 110 includes a first heating body 115, the first heating body 115 is a temperature-controlled heat-conducting plate, the temperature-controlled heat-conducting plate extends a plurality of first extending pillars 111 from an outer contour thereof to a direction close to a central axis thereof, the first extending pillars 111 are uniformly or non-uniformly distributed along the temperature-controlled heat-conducting plate, a first heating pillar 112 is further disposed on a side of the first extending pillar 111 adjacent to the microfluidic chip, the first heating pillar 112 is a heating region on the first heating module 110, that is, the first heating pillar 112 on the first heating module 110 is controlled to move to a reaction chamber on the microfluidic chip, so as to provide a suitable reaction temperature. The first heating body 115 and the first temperature controlled heating plate 113 are fixed by a first heat insulating fixing block 114.

In some embodiments, as shown in fig. 6, the second heating module 120 includes a second heating body 124, the second heating body 124 is a temperature-controlled heat conducting plate, the second heating body 124 is provided with a plurality of heat conducting pillars 121 near the microfluidic chip side, the heat conducting pillars 121 are detachably connected or non-detachably connected to the second heating body 124, and the second heating body 124 and the second temperature-controlled heating plate 122 are fixed by a heat insulation fixing column 123.

In some embodiments, as shown in fig. 5, the third heating module 130 includes a third heating body 135, the third heating body 135 is a temperature-controlled heat-conducting plate, the third heating body 135 extends a plurality of second extending pillars 131 along its outer peripheral profile to a position away from the central axis of the third heating body 135, the second extending pillars 131 are uniformly or non-uniformly distributed along the third heating body 135, a second heating pillar 132 is further disposed on the second extending pillar 131 and on the side of the microfluidic chip, and the second heating pillar 132 is a heating area on the third heating module 130, that is, the second heating pillar 132 on the third heating module 130 is controlled to move to a reaction chamber on the microfluidic chip to provide a suitable reaction temperature. The third heating body 135 and the third temperature controlled heating plate 133 are fixed by a third heat insulating fixing block 134.

It should be understood that the first, second and third do not refer to the importance of the object, but merely to distinguish between different objects.

When two or more heating modules are included, the heating modules may be provided as one or more of the first heating module 110, the second heating module 120, and the third heating module 130.

When a plurality of extending columns are arranged on one heating module, a gap exists between every two adjacent extending columns so as to be used for accommodating a heating zone on other heating modules. Specifically, when the heating module is the first heating module 110, the temperature control heat conduction plate extends a plurality of first extending columns 111 along the outer contour thereof toward the central axis, a gap is formed between two adjacent first extending columns 111 for accommodating the heat conduction column 121 on the second heating module 120 and the second heating column 132 on the third heating module 130, and a variable temperature region is formed between two adjacent first extending columns 111 (first heating columns), and the region includes the first heating column corresponding to the first temperature, the heat conduction column 121 corresponding to the second temperature, and the second heating column 132 corresponding to the third temperature. Furthermore, gaps exist among heating zones on different heating modules, and the gaps are 1cm-5cm, so that the temperatures among the heating modules are not influenced mutually. Specifically, in each variable temperature region, a gap of 1cm to 5cm exists between the first heating column 112 and the heat conduction column 121, a gap of 1cm to 5cm exists between the heat conduction column and the second heating column 132, and a gap of 1cm to 5cm exists between the second heating column and the next first heating column 112.

Example two

A PCR amplification detecting apparatus 100 includes a reaction module, a switchable incubation module and a fluorescence detecting module, which are sequentially disposed from top to bottom.

The reaction module comprises a microfluidic chip, and a plurality of reaction cavities can be arranged on the microfluidic chip so as to allow a plurality of reactions to be carried out simultaneously. In some embodiments, there are 16 PCR reaction chambers on the microfluidic chip, corresponding to 16 fluxes.

As shown in fig. 8, the rotary driving mechanism 103 in the incubation module comprises a rotary disk 1035, and the rotary disk 1035 further comprises at least one receiving area, through which the heating column passes to contact the reaction chamber on the microfluidic chip. In addition, the rotation driving structure 103 further includes a servo motor 1031, a servo motor riser 1032, a servo motor fixing plate 1033, and a chip fixing bracket 1034. The servo motor 1031 is fixed to the temperature control module fixing plate 1025 by the servo motor fixing plate 1033 and the servo motor riser 1032, and the chip fixing bracket 1034 is fixed to the servo motor 1031 to control the rotation of the turntable 1035.

The fluorescence detection module 104, as shown in fig. 9, is composed of a spectroscope 1041, a light emitter 1042, and an imaging detector 1043. When 16 PCR reaction cavities are arranged on the microfluidic chip, the first heating module 110, the second heating module 130 and the third heating module 120 are pushed in turn to contact with the PCR reaction cavities on the microfluidic chip under the action of the micro push rod 1013, and finally, the temperature of the PCR reaction cavities is controlled alternately. After the PCR reaction is finished, the light emitter 1042 is turned on, and the light reaches the PCR reaction cavity through the beam splitter 1041), is reflected to the beam splitter 1041 and is refracted to finally enter the imaging detector 1043 to realize the fluorescence detection. Specific implementation and application 1: mycoplasma Pneumoniae (MP) nucleic acid detection (PCR fluorescence method)

Adding a throat swab sample (35 years old and male sample) into 1mL of sterile physiological saline, shaking the mixture sufficiently, sucking the liquid into a centrifuge tube, centrifuging the liquid at 12,000RPM for 5 minutes, adding 100 mu L of precipitation liquid and 50 mu L of nucleic acid extracting solution into a storage tank of a microfluidic chip through manual operation, and operating the microfluidic chip at 2,000RPM (accelerated speed of 6,000RPM/s) to rotate for 7 minutes. After the nucleic acid extraction is completed, 50. mu.L of the supernatant can be transferred to the PCR reaction chamber by rotating the microfluidic chip at 1,500RPM (acceleration of 3,000RPM/s) for 10 seconds. A PCR amplification step: 50 ℃, 2 minutes and 1 cycle number; at 95 ℃ for 10 minutes, for 1 cycle; 55 ℃, 45 seconds and 45 cycles. The fluorescence was reported as FAM (excitation wavelength of 494nm, emission wavelength of 522nm), Ct value was measured as 40, and the result was indicated as a positive sample.

Specific implementation and application 2: verifying temperature accuracy of PCR temperature control module

Experimental parameters: the PCR amplification temperature was controlled to 50 ℃ (module a), 75 ℃ (module B), 95 ℃ (module C), cycle 50 ℃ → 95 → 75 ℃, for a total of 40 cycles. Experimental analysis: temperature measurements of the PCR reaction chamber were performed using a multiplex thermometer. Experimental objectives: the PCR reaction chamber temperature must be maintained at the set value. + -. 0.5 ℃. The experimental results are as follows: the module A (50 ℃) is switched to the module C (95 ℃), and the average temperature of the PCR reaction cavity can reach 95 ℃ +/-0.25 ℃ in 92 seconds; the module C (95 ℃) is switched to the module B (75 ℃), and the average temperature of the PCR reaction cavity can reach 75 ℃ +/-0.31 ℃ in 85 seconds; module B (75 ℃) was switched to module A (50 ℃) and the average temperature of the PCR reaction chamber reached 50 ℃. + -. 0.41 ℃ in 105 seconds. The above results show that the present invention can complete the PCR amplification step in a short time.

Fixed zone the various embodiments in this specification are described in a progressive manner, and like parts may be referred to one another, with each embodiment focusing on the differences from the other embodiments. In particular, for the system embodiment, since it is substantially similar to the method embodiment, the description is simple, and for the relevant points, reference may be made to the partial description of the method embodiment.