Dry-type multi-joint detection method and system for blood biochemical indexes based on micro multi-frequency light source

Abstract

The invention discloses a blood biochemical index dry-type multi-joint detection method and system based on a micro multi-frequency light source, and belongs to the technical field of blood biochemical detection. The detection host is of a small structure, and a micro multi-frequency optical module is arranged in the detection host; the method comprises the following steps: acquiring a detection chip, and dropwise adding trace blood; a detection chip is inserted into the detection host; the detection host identifies the detection chip, after identification is completed, the detection host carries out micro-fluidic control, filter pressing and micro-flow on the detection chip to a detection point to fully react with a correspondingly configured drying reagent, and then the detection host precisely drives the micro multi-frequency optical module to carry out corresponding optical scanning transparent detection on sequence point positions of the detection chip. According to the application, in-situ efficient filter pressing and micro-fluidic control on the detection chip are realized, precise optical detection is carried out, rapid and convenient biochemical detection is realized, and meanwhile, the accuracy of blood biochemical detection is greatly improved.

Description

Technical Field

[0001] The present application belongs to the field of biochemical detection, and specifically relates to the technical field of dry-type multiplex detection of blood biochemical indicators based on a micro multi-frequency light source. Background Art

[0002] The existing biochemical detection devices in the prior art have the following problems: large size, large amount of blood required for detection, long detection time, high detection cost, and limited location and environment for use of biochemical detection devices;

[0003] On the one hand, it is not easy to achieve miniaturization and precision requirements for light source solutions used in biochemical detection. In particular, the miniaturization and integration of light sources in multiple frequency bands is more difficult and cannot effectively guarantee precision, which is not conducive to the convenience and accuracy of detection.

[0004] On the other hand, general blood biochemical tests require the use of centrifugation technology to exclude blood cells to obtain serum and avoid the interference of blood cells in biochemical tests. The use of this centrifugation technology inevitably limits the miniaturization and convenience of blood biochemical tests.

[0005] There are also the difficulties in the precision microfluidics technology in miniaturization and the precision optical inspection micro-integration innovation;

[0006] However, the demand for blood biochemical testing, especially miniaturization and convenience, is becoming more and more prominent. The difficulty of miniaturization and convenience of blood biochemical testing lies in the difficulty of integrating and innovating the testing methods and testing systems.

[0007] Therefore, there is an urgent need to research and develop ways to overcome the difficulties in micro-integration of blood biochemical testing and provide micro-convenient, fast and accurate blood biochemical testing solutions. Summary of the invention

[0008] The present application discloses a blood biochemical index dry multiple detection method and system based on a micro multi-frequency light source, which is used to solve the difficulties of micro integration in current blood biochemical detection in the background technology and provide a micro convenient, fast and accurate blood biochemical detection solution.

[0009] According to one aspect of the present application, a blood biochemical index dry multiple detection method based on a micro multi-frequency light source is disclosed, and the method is applied to a blood biochemical index dry multiple detection system based on a micro multi-frequency light source, and the system includes a detection host and a detection chip;

[0010] The detection host is a small structure, and a micro multi-frequency optical module is built into the detection host, which is used to be driven to perform mobile scanning optical inspection on the detection chip;

[0011] The micro multi-frequency optical module includes a micro multi-frequency light source, which is used to selectively output at least one frequency band of detection light in a plurality of frequency bands according to the frequency band, and the detection light in the plurality of frequency bands includes the detection light in the first frequency band to the detection light in the second frequency band. Frequency band detection optical The detection light of the frequency band is is an integer greater than 1;

[0012] and a light receiving unit, for receiving the detection light and obtaining optical detection information;

[0013] The micro multi-frequency light source includes a first frequency band optical element to a frequency band optical element, used to generate the first frequency band detection light to the Frequency band detection light;

[0014] The micro-integrated optical path structure is used to conduct the detection light of the first frequency band to the An optical path for transmitting the frequency band detection light to the first light outlet;

[0015] The first light outlet is used for the detection light of the first frequency band to The frequency band detection light is emitted out of the micro multi-frequency light source;

[0016] and a collimation structure for detecting light in the first frequency band to the collimation of the frequency band detection light in the optical path;

[0017] The micro-integrated optical path structure includes a plurality of dichroic mirrors for reflecting or transmitting the first frequency band detection light to the second frequency band detection light. frequency band detection light, shortening and conducting the first frequency band detection light to the An optical path for transmitting the frequency band detection light to the first light outlet;

[0018] The method comprises:

[0019] Step 1: Obtain a detection chip, and drip a trace amount of blood to the sampling port of the detection chip; the detection chip has a filter press cavity, a sequence point, and a microchannel connecting the filter press cavity to the sequence point; the filter press cavity forms the sampling port on the upper surface of the detection chip; the filter press cavity has a filter press filter element in the detection chip for filtering blood cells to obtain serum; the sequence point includes multiple detection points;

[0020] The detection point forms a detection point cavity in the detection chip; the detection point cavity is connected to the filter press cavity through the microchannel in a one-to-one correspondence; the detection point cavity is configured with a corresponding dry reagent;

[0021] Step 2: inserting the detection chip into the detection host; the detection host identifies the detection chip, and after the identification is completed, the detection host performs microfluidics on the detection chip to precisely drive the blood in the filter pressure cavity of the detection chip to pass through the filter pressure element in the filter pressure cavity;

[0022] The serum obtained by filtration flows into the microfluidic channels one by one until all the detection point cavities at the sequence points are filled;

[0023] Under the control of physical and chemical conditions, the serum can fully react with the corresponding dry reagents in the detection point cavity. After the full reaction, all the detection point cavities remain filled and stand still waiting for detection;

[0024] Step 3: The detection host precisely drives the micro multi-frequency optical module to perform corresponding optical scanning and inspection on the sequence points of the detection chip according to the recognition result of the detection chip, so as to obtain the multi-link optical detection information of the detection chip;

[0025] Step 4: Analyze and calculate based on the multi-link optical detection information of the detection chip to obtain the detection result corresponding to the detection chip, wherein the detection result includes the multi-link biochemical index corresponding to the detection chip.

[0026] Preferably, the micro multi-frequency light source further comprises a second light outlet for transmitting the first frequency band detection light to the second The output light of at least one frequency band of the frequency band detection light;

[0027] The micro-integrated optical path structure shortens the conduction of the first frequency band detection light to the An optical path for transmitting detection light of at least one frequency band among the frequency band detection lights to the second light outlet.

[0028] Preferably, the micro-integrated optical path structure comprises a first dichroic mirror to a second dichroic mirror. Dichroic mirror,

[0029] Wherein, the first dichroic mirror is used for reflecting the detection light of the first frequency band to the second dichroic mirror;

[0030] The second dichroic mirror is used for transmitting the first frequency band detection light to the third dichroic mirror and reflecting the second frequency band detection light to the third dichroic mirror; Dichroic mirror, used to detect light in the first frequency band to the second The frequency band detection light is transmitted to the +1 dichroic mirror, where 1 to Integers, and The frequency band detection light is reflected to the +1 dichroic mirror;

[0031] No. Dichroic mirror, used to detect light in the first frequency band to the second 2 band detection light is transmitted to the Dichroic mirror and The frequency band detection light is reflected to the Dichroic mirror;

[0032] No. The dichroic mirror corresponds to the first light outlet and is used to detect the light from the first frequency band to the The 1st frequency band detection light is reflected to the first light outlet, and the The frequency band detection light is transmitted to the first light outlet.

[0033] Preferably, the first to second dichroic mirrors Dichroic mirror The dichroic mirrors are stacked end to end in an alternating pattern, extending in a wave shape.

[0034] The first frequency band optical element to the Frequency band optical components The optical elements are arranged alternately from the first dichroic mirror to the The side of the dichroic mirror.

[0035] Preferably, the collimating structure comprises an output lens, and the output lens is arranged between the micro-integrated optical path structure and the first light outlet.

[0036] Preferably, the collimating structure includes a first lens to a second lens. lenses, respectively arranged in the first frequency band optical element to the The side of the frequency band optical element; used to detect the first frequency band light generated corresponding to the first The frequency band detects the collimation of the light.

[0037] Preferably, the micro multi-frequency light source further comprises a power supply unit for supplying power from the first frequency band optical element to the The frequency band optical element selectively supplies single precision power and selectively outputs the first frequency band detection light to the Frequency band detection light;

[0038] When the first frequency band optical element to the When the power supply parameters of any optical element of the frequency band optical element are consistent twice, the parameters of the detection light outputted by it under the same optical path are consistent;

[0039] Among them, the power supply parameters include voltage and current;

[0040] Parameters of the detected light include light intensity.

[0041] Preferably, after the serum and the drying reagent have fully reacted, the microfluidic channel remains filled.

[0042] Preferably, the trace amount of blood is 1-4 drops.

[0043] Preferably, the filter press of the detection chip comprises a coarse filter element and a fine filter element which are arranged in sequence, the average pore size of the coarse filter element is larger than the average pore size of the fine filter element; and the filtration path of the coarse filter element is much larger than that of the fine filter element.

[0044] Preferably, the amount of the dried reagent is calculated based on the volume of the detection point cavity and the microfluidic channel corresponding to the corresponding detection point, to meet the amount of dried reagent required for the serum to fully react in the detection point cavity, and does not exceed the maximum amount of dried reagent required for the serum to fully react in the detection point cavity and the corresponding microfluidic channel.

[0045] Preferably, the detection chip has at least 7 types, and the 7 types correspond one by one to 7 corresponding detection types, namely liver function detection, kidney function detection, viral infection detection, glycolipid detection, pancreatic detection, kidney glycolipid detection and myocardial detection. Each detection type corresponds to multiple detection items, and each detection item corresponds to at least one detection point and at least one drying reagent.

[0046] Preferably, at least one detection point in the sequence of points of the detection chip is provided as a blank control point, and no dried reagent is configured in the detection point cavity corresponding to the blank control point.

[0047] Preferably, the detection chip has an identity module, and the detection host obtains the ID information of the detection chip by identifying the identity module of the detection chip. The ID information includes the type of the detection chip, the type information of the dried reagent in the sequence points, and the calibration curve.

[0048] Preferably, during the process of the detection host performing microfluidics on the detection chip, the serum obtained by filtration through the filter press is driven to flow, and the air in the microchannel and the sequence points is squeezed out from the detection chip to fill the sequence points.

[0049] Preferably, the method in which the detection host performs microfluidics on the detection chip comprises:

[0050] The detection chip is plugged into the detection host, and the sampling port of the detection chip faces upward. The detection host generates driving air pressure at the sampling port of the detection chip, and the driving air pressure drives the trace amount of blood to be filtered and micro-flown to the sequence points in the detection chip, and at the same time, gradually squeezes and discharges the air in the microchannel and detection point cavity in the detection chip until the serum obtained by filtration fills all the detection point cavities of the sequence points.

[0051] Preferably, the air in the microchannel and the detection point cavity in the detection chip is discharged along the plane direction of the detection chip, and the serum liquid is confined in the microchannel and the detection point cavity.

[0052] Preferably, the method in which the detection host performs microfluidics on the detection chip comprises:

[0053] The detection host configures an elastic pressure bowl at the sampling port of the detection chip, and uses precise control to move the elastic pressure bowl downward toward the sampling port of the detection chip to wrap the filter pressure cavity, and the elastic deformation generates driving air pressure.

[0054] Preferably, the outer side of the elastic pressure bowl has at least one pressing point, and the detection host drives the pressing point to move toward the detection chip. After the elastic pressure bowl contacts the detection chip, the displacement of the pressing point causes the elastic pressure bowl to produce elastic deformation, thereby generating driving air pressure.

[0055] The detection host precisely controls the rate of filtration driven by the driving air pressure, the flow rate of serum in the microchannel, and the relative pressure balance state maintained after the serum fills the sequence points through precise drive control of the pressing points.

[0056] Preferably, when the serum fills the sequence points, the elastic deformation of the elastic pressure bowl is reciprocatingly fine-tuned, and the driving air pressure is reciprocatingly fine-tuned, so that the serum is reciprocatingly filled in the detection point cavity, promoting a rapid and sufficient re-dissolution reaction between the serum and the dried reagent in the detection point cavity.

[0057] Preferably, the physical and chemical condition control includes temperature control; the temperature control makes the detection chip within a preset temperature range.

[0058] Preferably, the temperature control method includes using pulse heating under the detection chip to quickly heat the detection chip to a preset temperature range.

[0059] Preferably, in the process of the detection host performing corresponding optical mobile scanning and penetration inspection on the sequence points of the detection chip in step 3, at least two frequency bands of detection light are matched to each detection point in the sequence points for sequential optical inspection to obtain optical detection information corresponding to the detection point; the optical detection information of each detection point in the sequence points is summarized to obtain multi-link optical detection information of the detection chip;

[0060] The two frequency bands of detection light include main frequency band detection light, and the main frequency band detection light can be characteristically absorbed by the product of the reaction between the built-in desiccated reagent and the serum at the corresponding detection point, and is used for characteristic absorption detection of the detection point;

[0061] and a sub-band detection light, wherein the sub-band detection light cannot be characteristically absorbed by a product of a reaction between a built-in desiccated reagent and serum at a corresponding detection point, and is used for correction of characteristic absorption detection at the detection point;

[0062] The main frequency band detection light and the sub-frequency band detection light are the first frequency band detection light to the second frequency band detection light. The frequency band detects two types of light.

[0063] Preferably, the light receiving unit is a light intensity detection unit, which is used to detect the light intensity of the first frequency band detection light to the Nth frequency band detection light;

[0064] Using a light intensity detection unit to respectively detect the incident light intensity and the transmitted light intensity of the main frequency band detection light in the transmission light detection process;

[0065] As well as the incident light intensity and transmitted light intensity of the sub-band detection light.

[0066] Preferably, the method of transmitting light detection in the process of sequentially transmitting light detection by matching the corresponding main frequency band detection light and the sub-frequency band detection light to each detection point includes:

[0067] When the spot diameter of the main frequency band detection light and / or the sub-frequency band detection light corresponding to the matching is close to the diameter of the detection point, the detection light is driven to perform transmission light detection at the center of the detection point;

[0068] Furthermore, when the spot diameter of the matching main-band detection light and / or sub-band detection light at the sequence point is smaller than the diameter of the detection point and the difference is large, the detection light is driven to move within the plane diameter range of the detection point for scanning light detection.

[0069] Preferably, the detection host is provided with a first detection positioning point corresponding to the sequence point of the detection chip, and the detection light at the first detection positioning point B0 can directly illuminate the light receiving unit without blocking;

[0070] The first detection positioning point is arranged outside the detection chip or on the detection chip.

[0071] Preferably, the method in which the detection host precisely drives the micro multi-frequency optical module to perform corresponding optical movement scanning and inspection on the sequence points of the detection chip according to the recognition result of the detection chip includes:

[0072] The detection host drives the micro multi-frequency optical module to move to the first detection positioning point, and emits the first frequency band detection light from the first light outlet of the micro multi-frequency light source to the first detection position. The frequency band detection light can directly illuminate the light receiving unit without blocking, and obtain the first frequency band detection light to the The frequency band detects the incident light intensity of the light;

[0073] The detection host drives the micro multi-frequency optical module to move to the detection points of the sequence points in sequence, and performs transmitted light detection one by one. The incident light intensity of the main frequency band detection light and the sub-frequency band detection light matched at each detection point is consistent with the incident light intensity of the two frequency band detection lights corresponding to the first detection positioning point. After transmitting all the detection points, the transmitted light intensity of the main frequency band detection light and the sub-frequency band detection light corresponding to all the detection points is obtained;

[0074] The incident light intensity of the main-band detection light, the transmitted light intensity of the main-band detection light, the incident light intensity of the sub-band detection light and the transmitted light intensity of the sub-band detection light of all detection points are summarized to obtain the multi-link optical detection information of the detection chip.

[0075] Preferably, in step 4, the method of performing analysis and calculation based on the obtained multi-link optical detection information of the detection chip to obtain the detection result corresponding to the detection chip includes:

[0076] Preprocessing and calculating the multi-link optical detection information of the detection chip to obtain the concentration of the reaction product of the serum and the drying reagent in each detection point corresponding to the detection chip,

[0077] Then, using the concentration of the reaction product of the serum and the dried reagent at each detection point and the stoichiometric relationship reflected by the chemical equation based on the chemical reaction of the serum and the dried reagent corresponding to the detection point, the biochemical index of the detection item corresponding to the detection point is calculated from the concentration of the dried reagent reaction product corresponding to the detection point;

[0078] The biochemical indexes of the test items are analyzed and summarized to obtain the test results corresponding to the test chip, and the test results include the multi-test biochemical indexes corresponding to the test chip.

[0079] Preferably, the concentration calculation model of the dried reagent reaction product corresponding to the detection point is:

[0080] (1);

[0081] (2);

[0082]

[0083] (4);

[0084] By combining equations (1)-(4), we can solve:

[0085] ;

[0086] in, is the absorbance of the main frequency detection light in the detection point, is the absorbance of the sub-band detection light in the detection point, is the incident light intensity of the corresponding main frequency band detection light, The transmitted light intensity of the detection light for the corresponding main frequency band; is the incident light intensity of the corresponding sub-band detection light, is the transmission light intensity of the corresponding sub-band detection light; the main frequency band detection light and the sub-band detection light in the detection point are the first frequency band detection light to the Two types of frequency band detection light; a, b are calculation coefficients respectively;

[0087] A is the absorbance of the reaction product of the serum and the dried reagent in the detection point; K is the absorption coefficient of the reaction product of the serum and the dried reagent in the detection point, h is the optical path of the detection point, that is, the height of the detection point cavity, and c is the concentration of the reaction product of the serum and the dried reagent in the detection point.

[0088] On the other hand, the present application discloses a system that adopts the above-mentioned blood biochemical index dry multiple detection method based on micro multi-frequency light source.

[0089] Compared with the prior art, this application has the following beneficial effects:

[0090] The present application designs a new multi-inspection biochemical detection scheme, utilizes the detection chip in conjunction with a detection host with a microstructure, realizes in situ high-efficiency pressure filtration on the detection chip, obtains serum, and performs microfluidic channeling to enter the detection point of the detection chip to react with the dried reagent, and utilizes the micro multi-band integrated light source equipped with the detection host to perform optical joint inspection to realize fast and convenient biochemical detection, while greatly improving the accuracy of blood biochemical detection, and effectively solving the problems existing in the prior art such as large size of biochemical detection devices, large amount of blood required for detection, long detection time, high detection cost, and limited use location and environment of biochemical detection devices. BRIEF DESCRIPTION OF THE DRAWINGS

[0091] Figure 1 This is a block diagram of a multi-joint inspection system in an exemplary embodiment of the present application;

[0092] Figure 2 is a structural block diagram of a miniature multi-frequency light source in an exemplary embodiment of the present application;

[0093] Figure 3 A schematic diagram of a structure in which a second light outlet is configured for a miniature multi-frequency light source in an exemplary embodiment of the present application;

[0094] Figure 4 It is a schematic diagram of the structure of a micro integrated optical circuit in a micro multi-frequency light source in an exemplary embodiment of the present application;

[0095] Figure 5 This is a flow chart of a blood biochemical index dry multiplex detection method based on a micro multi-frequency light source in an exemplary embodiment of the present application;

[0096] Figure 6 A schematic diagram of the microfluidic structure of the detection chip in the exemplary embodiment of the present application;

[0097] Figure 7 A schematic block diagram of the detection type of the detection chip in the exemplary embodiment of the present application;

[0098] Figure 8 A schematic diagram of the sequence points of the detection chip in the exemplary embodiment of the present application;

[0099] Fig. 9 It is a schematic structural diagram of a filter press element of a detection chip in an exemplary embodiment of the present application;

[0100] Fig.10 is a cross-sectional schematic diagram of a detection chip in an exemplary embodiment of the present application;

[0101] Fig.11 A schematic diagram of the working of the detection host in an exemplary embodiment of the present application;

[0102] Fig.12 It is a schematic diagram of exhaust of the detection chip in the exemplary embodiment of the present application;

[0103] Fig.13 This is a schematic diagram of the working of the elastic pressure bowl in the detection host in the exemplary embodiment of the present application;

[0104] Fig.14 This is a schematic diagram of the position relationship between the elastic pressure bowl and the detection chip in the detection host in the exemplary embodiment of the present application;

[0105] Fig.15 This is a schematic diagram of the deformation of the elastic pressure bowl in the main unit in the exemplary embodiment of the present application;

[0106] Fig.16 A schematic diagram of fine-tuning the driving air pressure to draw serum from the detection point cavity in an exemplary embodiment of the present application;

[0107] Fig.17 A schematic diagram of the principle of optical inspection by scanning at sequential points in an exemplary embodiment of the present application;

[0108] Fig.18 It is a schematic diagram of the optical inspection principle at the detection point in the exemplary embodiment of the present application;

[0109] Fig.19 This is a schematic diagram of detection in a large light spot state in an exemplary embodiment of the present application;

[0110] Fig. 20 This is a schematic diagram of detection in a small light spot state in an exemplary embodiment of the present application;

[0111] In the figure, 1. a blood biochemical index dry multi-unit detection system based on a micro multi-frequency light source; 100. a detection host; 200. a detection chip; 11. a micro multi-frequency optical module; GY. a micro multi-frequency light source; GS. a light receiving unit; G1. a first frequency band optical element; G2. a second frequency band optical element; G , No. Band optical components; G +1, No. +1 Band Optics; G -1, No. -1 band optical components; G , No. Frequency band optical element; R1, first frequency band detection light; R02, second frequency band detection light; R , No. Frequency band detection light; R +1, No. +1 band detection light; R -1, No. -1 band detection light; R , No. Frequency band detection light; GL, micro integrated optical path structure; GZ, collimation structure; GC1, first light outlet; GD, power supply unit; GC2, second light outlet; S1, first dichroic mirror; S2, second dichroic mirror; S , No. Dichroic mirror; S +1, No. +1 dichroic mirror; S -1, No. -1 dichroic mirror; S , No. Dichroic mirror; T0, output lens; T1, first lens; T2, second lens; T , No. Lens; T +1, No. +1 lens; T , No. Lens; T , No. Lens; 300, trace blood; 301, serum; 201, injection port; 202, filter press cavity; 400, filter press cartridge; 203, sequence point; 204, microchannel; 205, detection point cavity; 206, dried reagent; B, detection point; 401, coarse filter cartridge; 4011, coarse filter path; 402, fine filter cartridge; 4021, fine filter path; J1, liver function test; J2, kidney function test; J3, virus infection test; J4, glycolipid test; J5, pancreas test; J6, kidney glycolipid test; J7, myocardial test; JXM, test items; 1000, driving air pressure; 2000, air; 101, identity recognition module; 20, identity module; 102, elastic pressure bowl; 1021, crimping point; L000, incident light of main-band detection light; L100, transmitted light of main-band detection light; L200, incident light of sub-band detection light; L300, transmitted light of sub-band detection light. DETAILED DESCRIPTION

[0112] The technical solution of this patent is further described in detail below in conjunction with specific implementation methods.

[0113] In order to make the purpose, technical solution and advantages of the present application more clearly understood, the present application is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and are not used to limit the present application.

[0114] In the description of the present application, it should be noted that the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inside", "outside" and the like indicate positions or positional relationships based on the positions or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation on the present application; the terms "first", "second", and "third" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance; in addition, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection, or it can be an indirect connection through an intermediate medium, or it can be a connection between the two elements. For those of ordinary skill in the art, the specific meanings of the above terms in the present application can be understood according to specific circumstances.

[0115] See also Figure 1-Figure 20 , an exemplary embodiment of the present application discloses a blood biochemical index dry multiple detection method based on a micro multi-frequency light source, the method is applied to a blood biochemical index dry multiple detection system 1 based on a micro multi-frequency light source, the system 1 includes a detection host 100 and a detection chip 200;

[0116] The detection host 100 is a small structure, and a micro multi-frequency optical module 11 is built in the detection host 100, which is used to be driven to perform mobile scanning optical inspection on the detection chip 100;

[0117] The micro multi-frequency optical module 11 includes a micro multi-frequency light source GY, which is used to selectively output at least one frequency band of detection light in a plurality of frequency bands according to the frequency band, and the detection light in the plurality of frequency bands includes the first frequency band detection light to the second frequency band detection light. Frequency band detection optical The detection light of the frequency band is is an integer greater than 1;

[0118] and a light receiving unit GS, for receiving the detection light and obtaining optical detection information;

[0119] The micro multi-frequency light source GY comprises a first frequency band optical element G1, a second frequency band optical element G2, ..., a Band Optical Components G , No. Band Optical Components G ,...,No. Band Optical Components G and Band Optical Components G ; Used to generate the first frequency band detection light R1, the second frequency band detection light R02, ..., the first Frequency band detection light R , No. +1 band detection light R +1,...,th -1 band detection light and frequency band detection light; among them, 1 to integer;

[0120] The micro-integrated optical circuit structure GL is used to conduct the first frequency band detection light R1 to the Frequency band detection light R The optical path transmitted to the first light outlet GC1;

[0121] The first light outlet GC1 is used for the detection light R1 in the first frequency band to Frequency band detection light R Outgoing light to the micro multi-frequency light source GY;

[0122] and a collimating structure GZ for detecting light R1 in the first frequency band to the second frequency band. Frequency band detection light R collimation in said optical path;

[0123] In an exemplary embodiment, the micro multi-frequency light source GY further includes a second light outlet GC2 for transmitting the first frequency band detection light R1 to the second frequency band detection light R2. Frequency band detection light R The detection light output is in at least one frequency band;

[0124] The micro-integrated optical circuit structure GL shortens the conduction of the first frequency band detection light R1 to the Frequency band detection light R The optical path in which the detection light of at least one frequency band is transmitted to the second light output port GC2.

[0125] In an exemplary embodiment, the collimating structure GZ comprises an output lens T0, which is arranged at the first Dichroic Mirror S and between the first light outlet GC1.

[0126] In an exemplary embodiment, the collimating structure GZ includes a first lens T1, a second lens T2, ..., a third lens T3, ... Lens T , No. +1 Lens T +1,...,th Lens T and Lens T ;

[0127] The optical elements G1 to G2 are respectively arranged in the first frequency band. Band Optical Components G and the corresponding micro-integrated optical path structure GL, respectively used for the first frequency band optical element G1 to the Band Optical Components G The first frequency band detection light R1 to the first frequency band detection light R2 Frequency band light R collimation;

[0128] The micro-integrated optical path structure GL includes a plurality of dichroic mirrors for reflecting or transmitting the first frequency band detection light R1 to the second frequency band detection light R2. Frequency band detection light R , shorten and conduct the first frequency band detection light R1 to the Frequency band detection light R The optical path transmitted to the first light outlet GC1;

[0129] In an exemplary embodiment, the micro-integrated optical path structure GL includes a first dichroic mirror S1, which is used to reflect the first frequency band detection light R1 to a second dichroic mirror S2;

[0130] A second dichroic mirror S2, used for transmitting the first-band detection light R1 to a third dichroic mirror (not shown) and reflecting the second-band detection light R02 to the third dichroic mirror (not shown);

[0131] No. Dichroic Mirror S , used for detecting light R1 to the first frequency band The frequency band detection light is transmitted to the Dichroic Mirror S +1 and Frequency band detection light R Reflect to Dichroic Mirror S +1;

[0132] No. Dichroic Mirror S , used for detecting light R1 to the first frequency band 2 band detection light is transmitted to the Dichroic Mirror S and Frequency band detection light R Reflect to Dichroic Mirror S ;

[0133] No. Dichroic Mirror S , corresponding to the first light outlet GC1, used for detecting the first frequency band light R1 to the 1 band detection light R Reflected to the first light outlet GC1, and the Frequency band detection light R Transmitted to the first light outlet GC1.

[0134] In an exemplary embodiment, the first dichroic mirror S1 to the second dichroic mirror S2 are Dichroic Mirror S common The dichroic mirrors are stacked end to end in an alternating pattern, extending in a wave shape.

[0135] The first frequency band optical elements G1 to G2 Band Optical Components G common The optical elements are arranged alternately from the first dichroic mirror S1 to the Dichroic Mirror S side.

[0136] In an exemplary embodiment, the micro multi-frequency light source GY further includes a power supply unit GD for supplying power to the first frequency band optical elements G1 to the second frequency band optical elements G2. Band Optical Components G Selectively supply single precision power and selectively output the first frequency band detection light to the Frequency band detection light;

[0137] When the first frequency band optical element G1 to the Band Optical Components G When the power supply parameters of any optical element are consistent twice, the parameters of the detection light outputted by it under the same optical path remain consistent;

[0138] Among them, the power supply parameters include voltage and current;

[0139] Parameters of the detected light include light intensity.

[0140] In an exemplary embodiment of the present application:

[0141] A blood biochemical index dry multiple detection method based on a micro multi-frequency light source, the method comprising:

[0142] Step 1, obtain the detection chip 200, and drip a trace amount of blood 300 to the injection port 201 of the detection chip 200; the detection chip 200 has a filter press cavity 202, a sequence point 203, and a microchannel 204 connecting the filter press cavity 202 to the sequence point 203; the filter press cavity 202 forms the injection port 201 on the upper surface of the detection chip 200; the filter press cavity 202 has a filter press filter element 400 in the detection chip 200 for filtering blood cells to obtain serum 301; the sequence point 203 includes a plurality of detection points B;

[0143] The detection point B is formed with a detection point cavity 205 in the detection chip 200; the detection point cavity 205 is connected to the filter press cavity 202 through the microchannel 204 in a one-to-one correspondence; the detection point cavity 205 is configured with a corresponding dry reagent 206;

[0144] In some embodiments, the detection chip 200 has at least 7 types, and the 7 types correspond one by one to 7 corresponding detection types, namely liver function detection J1, kidney function detection J2, viral infection detection J3, glycolipid detection J4, pancreatic detection J5, kidney glycolipid detection J6 and myocardial detection J7. Each detection type corresponds to multiple detection items JXM, and each detection item JXM corresponds to at least one detection point B and at least one drying reagent 206.

[0145] In an exemplary embodiment, the sequence points 203 of the detection chip 200 have at least one detection point B as a blank control point, and the detection point cavity 205 corresponding to the blank control point does not have a dried reagent 206 configured therein.

[0146] In an exemplary embodiment, the micro-amount of blood 300 is 1-4 drops, and the amount of serum required for the test is small, which is convenient.

[0147] In an exemplary embodiment, the pore size of the filter press element 400 is of the same order of magnitude as the cells of the blood to be detected. In an exemplary embodiment, the pore size of the filter press element 400 may be between 0.2 microns and 0.45 microns.

[0148] In an exemplary embodiment, the filter press filter element 400 includes a coarse filter element 401 and a fine filter element 402 arranged in sequence, and the average pore size of the coarse filter element 401 is larger than the average pore size of the fine filter element 402; the filtration path of the coarse filter element 401 is much larger than the fine filter element 402, that is, the coarse filtration path 4011 of the coarse filter element 401 is much larger than the fine filtration path 4021 of the fine filter element 402; this is conducive to making the filter press go smoothly while ensuring the filter press effect, effectively filtering blood cells, and avoiding the interference of blood cells on the detection;

[0149] In an exemplary embodiment, the amount of the dried reagent 206 is sufficient to ensure that the serum filling the detection point cavity 205 remains fully reacted with the dried reagent; and does not exceed the maximum amount of dried reagent 206 required for the serum 301 filling the microfluidic channel 204 and the detection point cavity 205 to fully react.

[0150] Step 2: insert the detection chip 200 into the detection host 100; the detection host 100 identifies the detection chip 200, and after the identification is completed, the detection host 100 performs microfluidics on the detection chip 200 to precisely drive the blood 300 in the filter pressure cavity 202 of the detection chip 200 to pass through the filter pressure element 400 in the filter pressure cavity 202;

[0151] The serum 301 obtained by filtration flows into the microchannels in a one-to-one correspondence until all the detection point cavities 205 of the sequence points 203 are filled;

[0152] Under the control of physical and chemical conditions, the serum 301 can fully react with the dried reagent 206 configured in the detection point cavity 205. After the full reaction, all the detection point cavities 205 remain filled and stand still to wait for detection;

[0153] In an exemplary embodiment, the detection chip 200 has an identity module 20, and the detection host 100 identifies the identity module 20 of the detection chip 200 through the identity recognition module 101 to obtain the ID information of the detection chip, wherein the ID information includes the type of the detection chip 200 and the type information of the dried reagent 206 in the sequence point 203 and the calibration curve.

[0154] In an exemplary embodiment, during the process of the detection host 100 performing microfluidics on the detection chip 200, the serum 301 obtained by filtering through the filter press 400 is driven to flow, squeezing the air 2000 in the microchannel 204 and the sequence points 203 out of the detection chip 200 and filling the sequence points 203.

[0155] The air 2000 in the microchannel 204 and the detection point cavity 205 in the detection chip 200 is discharged along the plane direction of the detection chip 200, and the serum 301 liquid is confined in the microchannel 204 and the detection point cavity 205;

[0156] In an exemplary embodiment, the method in which the detection host 100 performs microfluidics on the detection chip 200 includes:

[0157] The detection chip 200 is plugged into the detection host 100, and the sampling port 201 of the detection chip 200 faces upward. The detection host 100 generates a driving air pressure 1000 on the sampling port 201 of the detection chip 200, and the driving air pressure 1000 drives the trace blood 300 to be filtered and micro-flown to the sequence point 203 in the detection chip 200, and at the same time, gradually squeezes out the air 2000 in the microchannel 204 and the detection point cavity 205 in the detection chip 200 until the serum 301 obtained by the filtration fills all the detection point cavities 205 of the sequence point 203.

[0158] In an exemplary embodiment, the method in which the detection host 100 performs microfluidics on the detection chip 200 includes:

[0159] The detection host 100 configures an elastic pressure bowl 102 at the injection port 201 of the detection chip 200, and uses precise control to move the elastic pressure bowl 102 downward toward the injection port 201 of the detection chip 200, thereby wrapping and elastically deforming the filter cavity 202 of the detection chip 200 to generate a driving air pressure 1000.

[0160] In an exemplary embodiment, the outer side of the elastic pressure bowl 102 has at least one pressing point 1021, and the detection host 100 drives the pressing point 1021 to move toward the detection chip 200. After the elastic pressure bowl 102 contacts the detection chip 200, the displacement WY of the pressing point 1021 drives the elastic pressure bowl 102 to generate elastic deformation, thereby generating driving air pressure 1000;

[0161] The detection host 100 precisely controls the rate of the filter press driven by the driving air pressure 1000, the flow rate of the serum 301 in the microchannel 204, and the relative pressure balance state maintained after the serum 301 fills the sequence point 203 through precise driving control of the pressure contact point 1021.

[0162] In an exemplary embodiment, the detection host 100 fills and draws the serum 301 in the detection point cavity 205 by fine-tuning the driving air pressure 1000 , thereby promoting a rapid and sufficient reconstitution reaction between the dried reagent 206 and the serum 301 in the detection point cavity 205 .

[0163] In an exemplary embodiment, the detection host 100 performs physical and chemical condition control on the detection chip 200 , and the physical and chemical condition control includes temperature control; the temperature control makes the detection chip 200 within a preset temperature range.

[0164] In an exemplary embodiment, the temperature control method includes using pulse heating under the detection chip to quickly heat the detection chip to a preset temperature range.

[0165] In an exemplary embodiment, after the serum 301 fully reacts with the dried reagent 206 and is left at rest, the microchannel 204 and all the detection point cavities 205 remain filled.

[0166] In an exemplary embodiment, in step three, the detection host 100 precisely drives the micro multi-frequency optical module 11 to perform corresponding optical scanning and inspection on the sequence points 203 of the detection chip 200 according to the recognition result of the detection chip 200, so as to obtain the multi-link optical detection information of the detection chip 200;

[0167] In an exemplary embodiment, in the process of the detection host 100 performing corresponding optical mobile scanning inspection on the sequence points 203 of the detection chip 200 in step 3, at least two frequency bands of detection light are matched to each detection point B in the sequence points 203 for optical inspection in turn, and optical detection information corresponding to the detection point B is obtained; the optical detection information of each detection point B in the sequence points 203 is summarized to obtain multi-link optical detection information of the detection chip 200;

[0168] The two frequency bands of detection light include a main frequency band detection light, which can be characteristically absorbed by a product of the reaction between the built-in drying reagent 206 and the serum 301 at the corresponding detection point B, and is used for characteristic absorption detection of the detection point B;

[0169] and a sub-band detection light, wherein the sub-band detection light cannot be characteristically absorbed by a product of the reaction between the built-in drying reagent 206 and the serum 301 at the corresponding detection point B, and is used for characteristic absorption detection correction at the detection point B;

[0170] The main frequency band detection light and the sub-frequency band detection light are the first frequency band detection light R1 to the second frequency band detection light R2. Frequency band detection light R Two of them;

[0171] In an exemplary embodiment, the main frequency band detection light has at least four types, including the first frequency band detection light to the fourth frequency band detection light, and the center frequencies thereof are respectively , , , The sub-band detection light has at least one type, including a fifth band detection light, whose center frequency is .

[0172] In an exemplary embodiment, the center frequencies of the first frequency band detection light to the fourth frequency band detection light are respectively , , , The sub-band detection light has at least one type, including a fifth band detection light, whose center frequency is .

[0173] In an exemplary embodiment, the light receiving unit GS is a light intensity detection unit, which is used to detect the intensity of the first frequency band detection light to the first frequency band detection light. The frequency band detects the light intensity;

[0174] The light intensity detection unit 112 is used to detect the incident light intensity and the transmitted light intensity of the main frequency band detection light in the transmission light detection process respectively;

[0175] As well as the incident light intensity and transmitted light intensity of the sub-band detection light.

[0176] In an exemplary embodiment, the method of transmitting light detection in the process of sequentially transmitting light detection by matching the corresponding main frequency band detection light and the sub-frequency band detection light to each detection point includes:

[0177] When the spot diameter of the main frequency band detection light and / or the sub-frequency band detection light corresponding to the matching is close to the diameter of the detection point, the detection light is driven to perform transmission light detection at the center of the detection point;

[0178] In an exemplary embodiment, when the light spot presented by the matching corresponding main-band detection light and / or sub-band detection light at the sequence point is a large light spot DGB, and the diameter of the large light spot DGB is close to the diameter of the detection point, exemplarily, when the diameter of the large light spot DGB is larger than the diameter of the detection point and the difference is not large, the detection light is driven to perform a single transmission light inspection at the center of the detection point; exemplarily, when the diameter of the large light spot DGB is smaller than the diameter of the detection point and the difference is not large, the detection light is driven to perform multiple transmission light inspections at the center of the detection point;

[0179] In an exemplary embodiment, when the spot diameter of the matching main-band detection light and / or sub-band detection light at the sequence point is smaller than the diameter of the detection point and the difference is large, the detection light is driven to move within the plane diameter range of the detection point for scanning light detection.

[0180] In an exemplary embodiment, the detection host 100 is provided with a first detection positioning point B0 corresponding to the sequence point 203 of the detection chip 200, and the detection light in the first detection positioning point B0 can directly illuminate the light receiving unit GS without blocking;

[0181] In an exemplary embodiment, the first detection positioning point B0 is located outside the detection chip 200;

[0182] In an exemplary embodiment, the first detection positioning point B0 is located on the detection chip 200 ; a through hole is opened on the detection chip 200 corresponding to the first detection positioning point B0 .

[0183] In an exemplary embodiment, the method in which the detection host 100 precisely drives the micro multi-frequency optical module 11 to perform corresponding optical movement scanning inspection on the sequence points 203 of the detection chip 200 according to the recognition result of the detection chip 200 includes:

[0184] The sequence of points 203 includes detection points B1 to B common Testing points; is an integer greater than 1;

[0185] The detection host 100 drives the micro multi-frequency optical module 11 to move to the first detection positioning point B0, and performs optical detection on the first detection positioning point B0; the first frequency band detection light is sequentially emitted from the first light outlet GC1 of the micro multi-frequency light source to the first detection point B0; The frequency band detection light can directly illuminate the light receiving unit GS without blocking, and obtain the first frequency band detection light to the The frequency band detects the incident light intensity of the light;

[0186] The detection host 100 drives the micro multi-frequency optical module 11 to move to the detection point B1 to the detection point B1 of the sequence point in sequence. Perform scanning optical inspection of the sequence points to obtain the detection points B1 to B The corresponding transmitted light intensity of the transmitted light L100 of the main frequency band detection light and the transmitted light L300 of the sub-frequency band detection light;

[0187] And the first frequency band detection light used for transmission is transmitted to the first The incident light intensity of the two frequency bands of the detection light in the frequency band detection light is the same as the first frequency band detection light at the first detection positioning point B0 to the first frequency band detection light. The incident light intensities of the two corresponding frequency band detection lights in the frequency band detection light are consistent; from the first frequency band detection light at the first detection positioning point B0 to the first frequency band detection light at the first detection positioning point B1. The incident light intensity of the frequency band detection light is obtained from the corresponding detection point B1 to the detection point B The incident light intensity of the main-band detection light L000 and the incident light L200 of the sub-band detection light before the transmission detection point of the main-band detection light and the sub-band detection light corresponding to the position;

[0188] Summarize test point B1 to test point B The incident light intensity of the main frequency band detection light, the transmitted light intensity of the main frequency band detection light, the incident light intensity of the sub-frequency band detection light and the transmitted light intensity of the sub-frequency band detection light are obtained to obtain the multi-link optical detection information of the detection chip.

[0189] In an exemplary embodiment, the detection points B1 to B common The detection points are evenly spaced in a straight line, and the center of the first detection positioning point B0 is located between the detection points B1 and B and the distance between the center of the first detection positioning point B0 and the closest detection point is an integer multiple of the distance between adjacent detection points in the sequence of points.

[0190] In an exemplary embodiment, the detection points B1 to B common The detection points are arranged in a straight line with different intervals;

[0191] In an exemplary embodiment, the detection points B1 to B common The detection points are arranged in a curve.

[0192] Step 4: Analyze and calculate based on the obtained multi-link optical detection information of the detection chip 200 to obtain the detection result corresponding to the detection chip 200, wherein the detection result includes the multi-link biochemical index corresponding to the detection chip.

[0193] In an exemplary embodiment, the method of performing analysis and calculation based on the obtained multi-link optical detection information of the detection chip 200 in step 4 to obtain the detection result corresponding to the detection chip 200 includes:

[0194] Preprocessing and calculating the multi-link optical detection information of the detection chip 200 to obtain the concentration of the reaction product of the serum 301 and the dried reagent 206 in each detection point B corresponding to the detection chip 200,

[0195] Then, using the concentration of the reaction product of the serum 301 and the dried reagent 206 at each detection point B, and using the stoichiometric relationship reflected by the chemical equation based on the chemical reaction of the serum 301 and the dried reagent 206 corresponding to the detection point B, the biochemical index of the detection item JXM corresponding to the detection point B is estimated from the concentration of the reaction product of the dried reagent 206 corresponding to the detection point B;

[0196] The test results corresponding to the test chip are then obtained by analyzing and summarizing the biochemical indicators of the test item JXM, and the test results include the multi-test biochemical indicators corresponding to the test chip.

[0197] In an exemplary embodiment, the concentration calculation model of the dried reagent reaction product corresponding to the detection point B is:

[0198] (1);

[0199] (2);

[0200] (3);

[0201] (4);

[0202] By combining equations (1)-(4), we can solve:

[0203] ;

[0204] in, is the absorbance of the main frequency detection light in the detection point B, is the absorbance of the sub-band detection light in the detection point, is the incident light intensity of the corresponding main frequency band detection light, The transmitted light intensity of the detection light for the corresponding main frequency band; is the incident light intensity of the corresponding sub-band detection light, is the transmission light intensity of the corresponding sub-band detection light; the main frequency band detection light and the sub-band detection light in the detection point are the first frequency band detection light to the Two types of frequency band detection light; a, b are calculation coefficients respectively;

[0205] A is the absorbance of the reaction product of the serum and the dried reagent in the detection point; K is the absorption coefficient of the reaction product of the serum and the dried reagent in the detection point, h is the optical path of the detection point, that is, the height of the detection point cavity, and c is the concentration of the reaction product of the serum and the dried reagent in the detection point.

Claims

1. A blood biochemical index dry multiplex detection method based on a micro multi-frequency light source, characterized in that: include: Step 1: Get a test chip and drip a small amount of blood into the sampling port of the test chip; The detection chip comprises a filter press cavity, a sequence point, and a microchannel connecting the filter press cavity to the sequence point; the filter press cavity forms the sample inlet on the upper surface of the detection chip; the filter press cavity has a filter press filter element in the detection chip for filtering blood cells to obtain serum; the sequence point comprises a plurality of detection points; The detection point forms a detection point cavity in the detection chip; The detection point cavities are connected to the filter press cavities through microchannels in a one-to-one correspondence; the detection point cavities are equipped with corresponding drying reagents; Step 2: inserting the detection chip into the detection host; the detection host identifies the detection chip, and after the identification is completed, the detection host performs microfluidics on the detection chip to precisely drive the blood in the filter pressure cavity of the detection chip to pass through the filter pressure element in the filter pressure cavity; The serum obtained by filtration flows into the microfluidic channels one by one until all the detection point cavities at the sequence points are filled; Under the control of physical and chemical conditions, the serum can fully react with the corresponding dry reagents in the detection point cavity. After the full reaction, all the detection point cavities remain filled and stand still waiting for detection; Step 3: The detection host precisely drives the micro multi-frequency optical module to perform corresponding optical scanning and inspection on the sequence points of the detection chip according to the recognition result of the detection chip, so as to obtain the multi-link optical detection information of the detection chip; Step 4: Analyze and calculate based on the obtained multi-link optical detection information of the detection chip to obtain the detection result corresponding to the detection chip, wherein the detection result includes the multi-link biochemical index corresponding to the detection chip.

2. According to claim 1, the blood biochemical index dry multiple detection method based on a micro multi-frequency light source is characterized in that: The method is applied to a blood biochemical index dry multi-unit detection system based on a micro multi-frequency light source, the system comprising a detection host and a detection chip; The detection host is a small structure, and a micro multi-frequency optical module is built into the detection host, which is used to be driven to perform mobile scanning optical inspection on the detection chip; The micro multi-frequency optical module includes a micro multi-frequency light source, which is used to selectively output at least one frequency band of detection light in a plurality of frequency bands according to the frequency band, and the detection light in the plurality of frequency bands includes the detection light in the first frequency band to the detection light in the second frequency band. Frequency band detection optical The detection light of the frequency band is is an integer greater than 1; and a light receiving unit, for receiving the detection light and obtaining optical detection information; The micro multi-frequency light source includes a first frequency band optical element to a frequency band optical element, used to generate the first frequency band detection light to the Frequency band detection light; The micro-integrated optical path structure is used to conduct the detection light of the first frequency band to the An optical path for transmitting the frequency band detection light to the first light outlet; The first light outlet is used for the detection light of the first frequency band to The frequency band detection light is emitted out of the micro multi-frequency light source; and a collimation structure for detecting light in the first frequency band to the collimation of the frequency band detection light in the optical path; The micro-integrated optical path structure includes a plurality of dichroic mirrors for reflecting or transmitting the first frequency band detection light to the second frequency band detection light. frequency band detection light, shortening and conducting the first frequency band detection light to the The optical path of the frequency band detection light transmitted to the first light outlet.

3. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2 is characterized in that: The micro multi-frequency light source also includes a second light outlet for transmitting the first frequency band detection light to the second The output light of at least one frequency band of the frequency band detection light; The micro-integrated optical circuit structure shortens the conduction of the first frequency band detection light to the An optical path for transmitting detection light of at least one frequency band among the frequency band detection lights to the second light outlet.

4. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2 is characterized in that: The micro-integrated optical path structure includes a first dichroic mirror to a Dichroic mirror, Wherein, the first dichroic mirror is used for reflecting the detection light of the first frequency band to the second dichroic mirror; A second dichroic mirror, used for transmitting the first-band detection light to the third dichroic mirror and reflecting the second-band detection light to the third dichroic mirror; No. Dichroic mirror, used to detect light in the first frequency band to the second The frequency band detection light is transmitted to the Dichroic mirror, and The frequency band detection light is reflected to the Dichroic mirror, where 1 to integer; No. Dichroic mirror, used to detect light in the first frequency band to the second 2 band detection light is transmitted to the Dichroic mirror and The frequency band detection light is reflected to the Dichroic mirror; No. The dichroic mirror corresponds to the first light outlet and is used to detect the light from the first frequency band to the The 1st frequency band detection light is reflected to the first light outlet, and the The frequency band detection light is transmitted to the first light outlet.

5. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 4 is characterized in that: The first dichroic mirror to the Dichroic mirror The dichroic mirrors are stacked end to end in an alternating pattern, extending in a wave shape. The first frequency band optical element to the Frequency band optical components The optical elements are arranged alternately from the first dichroic mirror to the The side of the dichroic mirror.

6. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 4 is characterized in that: The collimating structure comprises an output lens, and the output lens is arranged between the micro-integrated optical path structure and the first light outlet.

7. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 4 is characterized in that: The collimating structure includes a first lens to a lenses, respectively arranged in the first frequency band optical element to the The side of the frequency band optical element; used to detect the first frequency band light generated corresponding to the first The frequency band detects the collimation of the light.

8. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The micro multi-frequency light source also includes a power supply unit for supplying power to the first frequency band optical element. The frequency band optical element selectively supplies single precision power and selectively outputs the first frequency band detection light to the Frequency band detection light; When the first frequency band optical element to the When the power supply parameters of any optical element of the frequency band optical element are consistent twice, the parameters of the detection light outputted by it under the same optical path are consistent; Among them, the power supply parameters include voltage and current; Parameters of the detected light include light intensity.

9. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: After the serum fully reacts with the drying reagent, the microfluidic channel remains filled.

10. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The micro amount of blood is 1-4 drops.

11. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The filter press of the detection chip comprises a coarse filter element and a fine filter element arranged in sequence, the average pore size of the coarse filter element is larger than the average pore size of the fine filter element; the filtration path of the coarse filter element is much larger than that of the fine filter element.

12. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The amount of the dried reagent is calculated based on the volume of the detection point cavity and the microfluidic channel corresponding to the corresponding detection point, and is sufficient to fill the detection point cavity with the serum for a full reaction, and does not exceed the maximum amount of dried reagent required for a full reaction of the serum to fill the detection point cavity and the corresponding microfluidic channel.

13. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The detection chip has at least 7 types, and the 7 types correspond one by one to 7 corresponding detection types. The 7 detection types are liver function detection, kidney function detection, virus infection detection, glycolipid detection, pancreatic detection, kidney glycolipid detection and myocardial detection. Each detection type corresponds to multiple detection items, and each detection item corresponds to at least one detection point and at least one dried reagent.

14. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The detection chip has at least one detection point in the sequence of points as a blank control point, and no drying reagent is configured in the detection point cavity corresponding to the blank control point.

15. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 13, characterized in that: The detection chip has an identity module, and the detection host obtains the ID information of the detection chip by identifying the identity module of the detection chip. The ID information includes the type of the detection chip, the type information of the dried reagent in the sequence point, and the calibration curve.

16. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: During the process of the detection host performing microfluidics on the detection chip, the serum obtained by filtering through the filter press is driven to flow, squeezing out the air in the microchannel and the sequence points from the detection chip and filling the sequence points.

17. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 16, characterized in that: The method for the detection host to perform microfluidics on the detection chip includes: The detection chip is plugged into the detection host, and the sampling port of the detection chip faces upward. The detection host generates driving air pressure at the sampling port of the detection chip, and the driving air pressure drives the trace amount of blood to be filtered and micro-flown to the sequence points in the detection chip, and at the same time, gradually squeezes and discharges the air in the microchannel and detection point cavity in the detection chip until the serum obtained by filtration fills all the detection point cavities of the sequence points.

18. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 17, characterized in that: The air in the microchannel and the detection point cavity in the detection chip is discharged along the plane direction of the detection chip, and the serum liquid is confined in the microchannel and the detection point cavity.

19. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 18, characterized in that: The method for the detection host to perform microfluidics on the detection chip includes: The detection host configures an elastic pressure bowl at the sampling port of the detection chip, and uses precise control to move the elastic pressure bowl downward toward the sampling port of the detection chip to wrap the filter pressure cavity, and the elastic deformation generates driving air pressure.

20. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 19, characterized in that: The outer side of the elastic pressure bowl has at least one pressing point, and the detection host drives the pressing point to move toward the detection chip. After the elastic pressure bowl contacts the detection chip, the displacement of the pressing point causes the elastic pressure bowl to produce elastic deformation, thereby generating driving air pressure; The detection host precisely controls the rate of filtration driven by the driving air pressure, the flow rate of serum in the microchannel, and the relative pressure balance state maintained after the serum fills the sequence points through precise drive control of the pressing points.

21. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 19, characterized in that: When the serum fills the sequence points, the elastic deformation of the elastic pressure bowl is reciprocated and fine-tuned, and the driving air pressure is reciprocated and fine-tuned, so that the serum is reciprocated and filled in the detection point cavity, promoting a rapid and full re-dissolution reaction between the serum and the dried reagent in the detection point cavity.

22. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: The physical and chemical condition control includes temperature control; the temperature control makes the detection chip within a preset temperature range.

23. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 22, characterized in that: The temperature control method includes using pulse heating under the detection chip to quickly heat the detection chip to a preset temperature range.

24. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 2, characterized in that: In the step 3, during the optical mobile scanning and penetrating inspection of the sequence points of the detection chip by the detection host, at least two frequency bands of detection light are matched to each detection point in the sequence points in turn for penetrating optical inspection to obtain optical detection information corresponding to the detection point; the optical detection information of each detection point in the sequence points is summarized to obtain multi-link optical detection information of the detection chip; The two frequency bands of detection light include main frequency band detection light, and the main frequency band detection light can be characteristically absorbed by the product of the reaction between the built-in desiccated reagent and the serum at the corresponding detection point, and is used for characteristic absorption detection of the detection point; and a sub-band detection light, wherein the sub-band detection light cannot be characteristically absorbed by a product of a reaction between a built-in desiccated reagent and serum at a corresponding detection point, and is used for correction of characteristic absorption detection at the detection point; The main frequency band detection light and the sub-frequency band detection light are the first frequency band detection light to the second frequency band detection light. The frequency band detects two types of light.

25. The blood biochemical index dry multiplex detection method based on a micro multi-frequency light source according to claim 24, characterized in that: The light receiving unit is a light intensity detection unit, which is used to detect the light intensity of the first frequency band detection light to the Nth frequency band detection light; Using a light intensity detection unit to respectively detect the incident light intensity and the transmitted light intensity of the main frequency band detection light in the transmission light detection process; As well as the incident light intensity and transmitted light intensity of the sub-band detection light.

26. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 24, characterized in that: The method for transmission light inspection in the process of sequentially transmitting light inspection by matching the corresponding main frequency band detection light and the sub-frequency band detection light to each detection point includes: When the spot diameter of the main frequency band detection light and / or the sub-frequency band detection light corresponding to the matching is close to the diameter of the detection point, the detection light is driven to perform transmission light detection at the center of the detection point; Furthermore, when the spot diameter of the matching main-band detection light and / or sub-band detection light at the sequence point is smaller than the diameter of the detection point and the difference is large, the detection light is driven to move within the plane diameter range of the detection point for scanning light detection.

27. The blood biochemical index dry multiplex detection method based on a micro multi-frequency light source according to claim 24, characterized in that: The detection host is provided with a first detection positioning point at the sequence point position corresponding to the detection chip, and the detection light in the first detection positioning point B0 can directly illuminate the light receiving unit without blocking; The first detection positioning point is arranged outside the detection chip or on the detection chip.

28. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 27, characterized in that: The method in which the detection host precisely drives the micro multi-frequency optical module to perform corresponding optical movement scanning and penetration inspection on the sequence points of the detection chip according to the recognition result of the detection chip includes: The detection host drives the micro multi-frequency optical module to move to the first detection positioning point, and emits the first frequency band detection light from the first light outlet of the micro multi-frequency light source to the first detection position. The frequency band detection light can directly illuminate the light receiving unit without blocking, and obtain the incident light intensity of the first frequency band detection light to the second frequency band detection light; The detection host drives the micro multi-frequency optical module to move to the detection points of the sequence points in sequence, and performs transmitted light detection one by one. The incident light intensity of the main frequency band detection light and the sub-frequency band detection light matched at each detection point is consistent with the incident light intensity of the two frequency band detection lights corresponding to the first detection positioning point. After transmitting all the detection points, the transmitted light intensity of the main frequency band detection light and the sub-frequency band detection light corresponding to all the detection points is obtained; The incident light intensity of the main-band detection light, the transmitted light intensity of the main-band detection light, the incident light intensity of the sub-band detection light and the transmitted light intensity of the sub-band detection light of all detection points are summarized to obtain the multi-link optical detection information of the detection chip.

29. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to any one of claims 2 to 28, characterized in that: In step 4, the method of performing analysis and calculation based on the obtained multi-link optical detection information of the detection chip to obtain the detection result corresponding to the detection chip includes: Preprocessing and calculating the multi-link optical detection information of the detection chip to obtain the concentration of the reaction product of the serum and the drying reagent in each detection point corresponding to the detection chip, Then, using the concentration of the reaction product of the serum and the dried reagent at each detection point and the stoichiometric relationship reflected by the chemical equation based on the chemical reaction of the serum and the dried reagent corresponding to the detection point, the biochemical index of the detection item corresponding to the detection point is calculated from the concentration of the dried reagent reaction product corresponding to the detection point; The biochemical indexes of the test item are analyzed and summarized to obtain the test results corresponding to the test chip, and the test results include the multi-test biochemical indexes corresponding to the test chip.

30. The blood biochemical index dry multiple detection method based on a micro multi-frequency light source according to claim 29, characterized in that: The concentration calculation model of the dried reagent reaction product corresponding to the detection point is: （1）； （2）； （3）； （4）； By combining equations (1)-(4), we can solve: ； in, is the absorbance of the main frequency detection light in the detection point, is the absorbance of the sub-band detection light in the detection point, is the incident light intensity of the corresponding main frequency band detection light, The transmitted light intensity of the detection light for the corresponding main frequency band; is the incident light intensity of the corresponding sub-band detection light, is the transmission light intensity of the corresponding sub-band detection light; the main frequency band detection light and the sub-band detection light in the detection point are the first frequency band detection light to the Two types of frequency band detection light; a, b are calculation coefficients respectively; A is the absorbance of the reaction product of the serum and the dried reagent in the detection point; K is the absorption coefficient of the reaction product of the serum and the dried reagent in the detection point, h is the optical path of the detection point, that is, the height of the detection point cavity, and c is the concentration of the reaction product of the serum and the dried reagent in the detection point.

31. A system using the blood biochemical index dry multiple detection method based on a micro multi-frequency light source as claimed in claim 30.

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