Blood reaction analyzer and reaction liquid mixing method

Abstract

The invention discloses a blood reaction analyzer and a reaction liquid mixing method.The blood reaction analyzer comprises a cup body, the upper end of the cup body is an open cup opening, the lower end of the cup body is a discharge outlet, and the cup body comprises a filling section and a reaction light detection section which are sequentially arranged in the direction from the cup opening to the discharge outlet; the reaction light detection section is an area where a biological sample reacts with a reagent, the outer wall of the filling section is communicated with a reagent inlet pipe, and the reagent inlet pipe is suitable for being communicated with a reagent filling pipeline used for filling the reagent. Therefore, the reagent can be added into the reaction cup through the reagent filling pipeline and the reagent inlet pipe, and compared with the condition that the reagent inlet pipe is arranged in the reaction light detection area, in the process of uniformly mixing the biological sample and the reagent, the reaction liquid is not easy to enter the reagent inlet pipe and is not easy to permeate with the reagent, so that the pollution to the reagent can be reduced, and the reaction quality is improved. And finally, the accuracy of optical analysis results is improved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a blood reaction analyzer and a reaction solution mixing method. Background Art

[0002] The existing reaction devices for blood sample analysis are usually reaction cups. The upper end of the reaction cup is provided with a cup mouth, the lower end is provided with a discharge port, and a reagent inlet tube communicating with the inner cavity of the reaction cup is provided on the side wall of the reaction cup. The biological sample to be detected enters the inner cavity of the reaction cup through the cup mouth, and the reagent reacting with the biological sample is injected into the inner cavity of the reaction cup through the reagent inlet tube. After the reagent and the biological sample react in the inner cavity of the reaction cup, then an optical device is used to perform optical analysis on the reaction solution in the inner cavity of the reaction cup.

[0003] In the prior art, the position where the reagent inlet tube communicates with the reaction cup is the same as the position where the reagent and the biological sample react. The reacted reaction solution easily enters the reagent inlet tube, thereby contaminating the reagent filling pipeline communicating with the reagent inlet tube; moreover, during the reaction of the reagent and the biological sample, in order to ensure that the reagent and the biological sample can be fully mixed, it is necessary to perform suction and discharge mixing operations on the reaction solution, further increasing the risk of contaminating the reagent filling pipeline by the reaction solution.

[0004] In view of the above deficiencies, it is necessary to design a blood reaction analyzer and a reaction solution mixing method. Summary of the Invention

[0005] Therefore, the technical problem to be solved by the present invention is that in the prior art, the reagent inlet tube communicates with the reaction area, resulting in easy mutual penetration between the reagent and the reaction solution, thereby affecting the accuracy of the analysis result. Thus, a blood reaction analyzer and a reaction solution mixing method are provided.

[0006] To solve the above technical problem, the technical solution of the present invention is as follows:

[0007] A blood reaction analyzer, comprising:

[0008] A complete blood count detection component;

[0009] A specific protein detection component, the specific protein detection component includes a reaction cup, the reaction cup includes a cup body, the upper end of the cup body is an open cup mouth, the lower end is a discharge port, the cup body includes a filling section and a reaction and optical detection section sequentially arranged from the cup mouth to the discharge port direction, the reaction and optical detection section is the area where the biological sample and the reagent react, the outer wall of the filling section is communicated with a reagent inlet tube, and the reagent inlet tube is adapted to communicate with a reagent filling pipeline for injecting a reagent.

[0010] Further, the opening of the reagent inlet tube communicates with a reduced-diameter interface tube, and at least two interfaces are provided at one end of the reduced-diameter interface tube facing away from the cup body. One of the interfaces is connected to the flushing pipeline, and the remaining interfaces are connected to the reagent filling pipeline.

[0011] Further, at least two reagent filling branch pipelines are provided at one end of the reagent filling pipeline facing away from the cup body.

[0012] Further, the diameter of the reduced-diameter interface tube is larger than the diameter of any one of the reagent filling branch pipelines.

[0013] Further, a flushing pipeline control valve for controlling the on-off of the flushing pipeline is provided on the flushing pipeline.

[0014] Further, the reagent inlet tube is inclined, and the position of the end of the reagent inlet tube connected to the reagent filling pipeline is higher than the position of the end of the reagent inlet tube connected to the reaction optical detection section.

[0015] Further, the specific protein detection assembly further includes:

[0016] A fixed seat, on which an installation cavity with a top opening is provided;

[0017] A light source assembly, installed on the fixed seat and located on the light incident surface side of the cup body, adapted to emit detection light to the light incident surface of the cup body;

[0018] A light receiving and analyzing assembly, installed on the fixed seat and located on the light exit surface side of the cup body, adapted to receive the detection light emitted from the light exit surface of the cup body, and the light exit surface is arranged opposite to the light incident surface.

[0019] Further, a liquid guiding structure is connected around the outer wall surface of the cup body. A liquid guiding channel communicating with the outer wall surface of the cup body is formed on the liquid guiding structure. The liquid guiding structure is located at the top opening of the installation cavity, and the reaction liquid overflowing from the cup mouth is adapted to be discharged outward through the liquid guiding channel.

[0020] The technical solution of the present invention has the following advantages:

[0021] The blood reaction analyzer provided by the present invention includes a complete blood count detection component and a specific protein detection component. The specific protein detection component includes a reaction cup, which includes a cup body. The upper end of the cup body is an open cup mouth, and the lower end is a discharge port. The cup body includes a filling section and a reaction optical detection section arranged in sequence from the cup mouth to the discharge port. The reaction optical detection section is the area where the biological sample and the reagent react. A reagent inlet tube is connected to the outer wall of the filling section. The reagent inlet tube is adapted to be connected to a reagent filling pipeline for injecting the reagent. In this way, the reagent can be added into the reaction cup through the reagent filling pipeline and the reagent inlet tube. Compared with setting the reagent inlet tube in the reaction optical detection area, during the mixing process of the biological sample and the reagent, the reaction liquid is not easily introduced into the reagent inlet tube, and the osmosis phenomenon with the reagent is not likely to occur, thereby reducing the pollution of the reagent and ultimately improving the accuracy of the optical analysis result.

[0022] A blood reaction analyzer, comprising:

[0023] A complete blood count detection component;

[0024] A specific protein detection component, the specific protein detection component includes a cup body, the upper end of the cup body is an open cup mouth, the lower end is a discharge port, the cup body includes a filling section and a reaction optical detection section arranged in sequence from the cup mouth to the discharge port, the reaction optical detection section is the area where the biological sample and the reagent react, a reagent inlet tube is connected to the outer wall of the filling section, the reagent inlet tube is adapted to be connected to a reagent filling pipeline for injecting the reagent, discharging the reaction liquid through the discharge port, and injecting air bubbles into the reaction cup by a power device through the discharge port to mix the reaction liquid.

[0025] Further, the specific protein detection component further includes a three-way valve and a buffer cavity. The power device is connected to the first opening of the three-way valve through a first pipeline. The second opening and the third opening of the three-way valve are respectively connected to the diluent through a second pipeline and communicate with the reaction optical detection section through a flushing pipeline.

[0026] The technical solution of the present invention has the following advantages:

[0027] In the blood reaction analyzer provided by the present invention, air bubbles are injected into the reaction cup by a power device through the discharge port to mix the reaction liquid. Compared with the design of mixing the reaction liquid by repeatedly sucking and discharging the liquid, the surging of the reaction liquid during the mixing process is not large, thereby avoiding the reaction liquid from surging into the reagent inlet and the reagent inlet tube.

[0028] A method for mixing a reaction liquid, based on the blood reaction analyzer described in the foregoing claims, includes the following steps:

[0029] The power device sucks the diluent along the second pipeline, and the diluent enters the first pipeline;

[0030] Disconnect the second pipeline;

[0031] The diluent in the first pipeline is sent into the buffer cavity by the power device, and the air in the buffer cavity is pressed into the reaction cup to form bubbles, and the bubbles form a turbulent flow to mix the reaction solution.

[0032] The method for mixing the reaction solution provided by the present invention includes the following steps: the diluent is sucked along the second pipeline by the power device, and the diluent enters the first pipeline; the second pipeline is disconnected; the diluent in the first pipeline is sent into the buffer cavity by the power device, and the air in the buffer cavity is pressed into the reaction cup to form bubbles, and the bubbles form a turbulent flow to mix the reaction solution. Compared with the design of mixing the reaction solution by repeatedly sucking and discharging the liquid, the surging of the reaction solution during the mixing process is not large, and thus the reaction solution can be prevented from surging into the reagent inlet and the reagent inlet pipe. Description of the Drawings

[0033] In order to more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the following will briefly introduce the drawings required for use in the description of the specific embodiments or the prior art. Obviously, the drawings in the following description are some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0034] Figure 1 Is a three-dimensional schematic diagram of the blood reaction analyzer of the present invention;

[0035] Figure 2 Is a three-dimensional schematic diagram of the connection between the reaction cup and the fixing seat of the specific protein detection component in the present invention;

[0036] Figure 3 Is a three-dimensional schematic diagram of the cup body in the present invention;

[0037] Figure 4 Is a three-dimensional schematic diagram of the light-transmitting member in the present invention;

[0038] Figure 5 Is a three-dimensional schematic diagram of the combination of the cup body and the light-transmitting member in the present invention;

[0039] Figure 6 Is a schematic cross-sectional structure diagram of the reaction cup in the present invention;

[0040] Figure 7 Is a schematic plan structure diagram of the blood reaction analyzer of the present invention.

[0041] Explanation of the reference numerals:

[0042] A, Blood reaction analyzer; B, Complete blood count detection component; C, Specific protein detection component; C1, Fixed seat; C2, Light source component; C3, Pressing component; C4, Light receiving and analyzing component; C5, Side opening; C6, Card slot; D, Power device; E, Three-way valve; F, Buffer cavity; G, Sampler; 1, Cup body; 10, Cup mouth; 11, Filling section; 111, Reagent inlet tube; 12, Reaction and light detection section; 121, Window; 13, Liquid discharge section; 131, Transition part; 132, Discharge pipe; 14, Discharge port; 2, Translucent part; 3, Rib; 4, Liquid guiding structure; 41, Liquid guiding plate; 42, Baffle; 43, Reinforcing plate; 44, Liquid guiding channel; 51, Reducing interface pipe; 52, Reagent filling pipeline; 521, Reagent filling branch pipeline; 61, First pipeline; 62, Second pipeline; 63, Main pipeline; 631, Flushing pipeline; 6310, Flushing pipeline control valve; 632, Liquid inlet pipeline; 6320, Liquid inlet control valve; 64, Air inlet pipeline; 65, Liquid discharge tail pipe. Detailed implementation manners

[0043] Next, the technical solutions of the present invention will be clearly and completely described in conjunction with the accompanying drawings. Obviously, the described embodiments are part of the embodiments of the present invention, rather than all of them. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts fall within the protection scope of the present invention.

[0044] In the description of the present invention, it should be noted that the orientation or positional relationship indicated by the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inside", "outside", etc. is based on the orientation or positional relationship shown in the accompanying drawings. It is only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus cannot be understood as a limitation to the present invention. In addition, the terms "first", "second", and "third" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance.

[0045] In the description of the present invention, it should be noted that unless otherwise clearly specified and limited, the terms "installation", "connection", and "connection" 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 directly connected or indirectly connected through an intermediate medium, and it can be the communication inside two elements. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to specific situations.

[0046] In addition, the technical features involved in different embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.

[0047] As shown Figures 1 to 7 in the figure, this embodiment provides an optical reaction analyzer. The optical reaction analyzer A includes a blood routine detection component B and a specific protein detection component C. Since the improvement of the present invention lies in the specific protein detection component C, the blood routine detection component B will not be described in detail here. The specific protein detection component C mainly includes a reaction cup C0, a fixing seat C1, a light source assembly C2, a light receiving and analyzing assembly C4, a liquid guiding structure 4, a power device D, a three-way valve E, and a buffer cavity F.

[0048] The opposite sides of the reaction cup C0 are respectively a light incident surface and a light exit surface.

[0049] An installation cavity (not labeled) for the reaction cup C0 is provided inside the fixing seat C1. The reaction cup C0 extends into the installation cavity from the top opening of the installation cavity, so that the lower end of the reaction cup C0 is located inside the installation cavity. The installation cavity has a top opening and two side openings C5. The width of the side opening C5 is smaller than the width of the installation cavity. The two side openings C5 are opened on the opposite side surfaces of the fixing seat C1 corresponding to the installation cavity. The two side openings C5, the light source assembly C2, and the light receiving and analyzing assembly C4 are respectively located on four different side surfaces of the installation cavity. Specifically, the light source assembly C2 is fixedly installed on the fixing seat C1 and is located on one side of the light incident surface of the reaction cup C0, and is used to emit detection light to the light incident surface of the reaction cup C0. The light receiving and analyzing assembly C4 is installed on the fixing seat C1 and is located on one side of the light exit surface of the reaction cup C0, and is used to receive the detection light emitted from the light exit surface of the reaction cup C0. The optical path channel formed by the detection light emitted by the light source assembly C2 passing through the reaction cup C0 and being received by the light receiving and analyzing assembly C4 is the optical detection channel. In this embodiment, two reaction cups C0 are installed in the installation cavity, and each reaction cup C0 is correspondingly provided with a light source assembly C2 and a light receiving and analyzing assembly C4. It can be understood that when only one reaction cup C0 is installed in the installation cavity, the fixing seat C1 can only have a side opening C5 on one side.

[0050] The reaction cup C0 includes a cup body 1 that is larger at the top and smaller at the bottom. The upper end of the cup body 1 is an open cup mouth 10, and the lower end is a discharge port 14. The cup body 1 includes a filling section 11, a reaction and light detection section 12, and a liquid discharge section 13 arranged in sequence from the cup mouth 10 to the discharge port 14. The outer diameter of the cup mouth 10 is larger than the outer diameter of the discharge port 14. The discharge port 14 of the cup body 1 is connected to the buffer cavity F through an air inlet pipeline 64 (as Figure 7 shown).

[0051] A reagent inlet is provided on the outer wall of the filling section 11. The reason for setting the reagent inlet on the outer wall of the filling section 11 instead of on the outer wall of the reaction and optical detection section 12 is to avoid the risk that biological samples (such as blood samples) and reagents move upward due to fluctuations during the mixing process and enter the reagent inlet, contaminate the reagent pipeline, or even cause the penetration of the reaction solution and the reagent. A reagent inlet tube 111 is provided on the outer wall of the filling section 11 corresponding to the reagent inlet. In this embodiment, the reagent inlet tube 111 is integrally formed with the cup body 1. The reagent filling pipeline 52 is connected to the reagent inlet tube 111. In this way, the reagent can be added into the reaction cup C0 through the reagent filling pipeline 52, the reagent inlet tube 111, and the reagent inlet in sequence. The reagent inlet tube 111 is inclined, and the position of the end of the reagent inlet tube 111 connected to the reagent filling pipeline 52 is higher than the position of the end of the reagent inlet tube 111 connected to the reaction and optical detection section 12. In this way, on the one hand, it is beneficial for the reagent to smoothly enter the reaction cup C0, and on the other hand, it can further avoid the risk that biological samples and reagents enter the reagent inlet tube 111 and the reagent filling pipeline 52 due to fluctuations during the mixing process, resulting in contamination of the reagent or the reagent pipeline and thus affecting the accuracy of the analysis results.

[0052] The opening of the reagent inlet tube 111 facing away from the cup body 1 is communicated with a variable-diameter interface tube 51. At least two interfaces are provided at one end of the variable-diameter interface tube 51 facing away from the cup body 1. One interface is connected to the flushing pipeline 631 (as Figure 7 shown), and the other interface is connected to the reagent filling pipeline 52. In this embodiment, at least two reagent filling branch pipelines 521 are provided at one end of the reagent filling pipeline 52 facing away from the cup body 1. The diameter of the variable-diameter interface tube 51 is larger than the diameter of any one of the reagent filling branch pipelines 521, so as to inject two or more reagents into the reaction cup C0 simultaneously through the reagent filling branch pipelines 521. In this way, it is convenient to inject two or more reagents into the reaction cup C0 simultaneously, which can improve the convenience of reagent filling and better adapt to the situation with strict requirements for the simultaneity of reagent filling. The extending directions of the reagent inlet tubes 111 all point to the side opening C5. In this way, the side opening C5 can provide an extending space for the reagent inlet tubes 111 and the variable-diameter interface tube 51, so that the interfaces of the variable-diameter interface tube 51 can be exposed to facilitate reagent filling.

[0053] The reaction and light detection section 12 is the area where the biological sample and the reagent react. Windows 121 are respectively provided on the light incident surface and the light exiting surface of the reaction and light detection section 12. Two light-transmitting members 2 are respectively disposed at the two windows 121 and seal the corresponding windows 121. In this embodiment, convex strips 3 are respectively provided on both sides of the light-transmitting member 2, and the two convex strips 3 are respectively bonded and fixed or heat-melted and fixed to both sides of the light-transmitting member 2, or interference-fixed. At the same time, the light-transmitting member 2 is bonded or heat-melted and fixed to the side wall of the cup body 1 between the two convex strips 3. The setting of the convex strips 3 can increase the connection area between the light-transmitting member 2 and the cup body 1. At the same time, the convex strips 3 can protect the light-transmitting member 2 from the side and prevent the light-transmitting member 2 from falling off the cup body 1 due to lateral external force. Since the light-transmitting member 2 and the cup body 1 are respectively independently formed, the light-transmitting member 2 can be made of a light-transmitting material with good wear resistance and dirt resistance. In this embodiment, the cup body 1 is made of plastic, and the light-transmitting member 2 is made of glass or quartz material.

[0054] The liquid discharge section 13 includes a connected conical transition portion 131 and a discharge pipe 132. The discharge port 14 is located at the end of the discharge pipe 132 far from the reaction and light detection section 12. The setting of the conical transition portion 131 facilitates the complete discharge of the reaction liquid in the cup body 1 and avoids the residual reaction liquid affecting the analysis result of the next biological sample.

[0055] The liquid guiding structure 4 is connected and disposed around the outer wall surface of the cup body 1, and the position of the liquid guiding structure 4 is lower than the position of the cup mouth 10. A liquid guiding channel 44 communicating with the outer wall surface of the cup body 1 is formed on the liquid guiding structure 4. The reaction liquid overflowing from the cup mouth 10 is guided through the liquid guiding channel 44 and discharged outward. In this way, the overflowing reaction liquid can be prevented from polluting the optical detection channel inside the optical reaction analyzer and even damaging the optical devices, improving the accuracy of the analysis result of the optical reaction analyzer and reducing the failure rate of the optical reaction analyzer. In this embodiment, the liquid guiding structure 4 and the cup body 1 are integrally formed, and the liquid discharge direction of the liquid guiding channel 44 avoids the side opening C5. For example, the liquid discharge direction of the liquid guiding channel 44 is set along the connection line direction of the light source assembly C2 and the light receiving and analyzing assembly C4. In this way, it can be prevented that the reaction liquid discharged from the liquid guiding channel 44 enters the installation cavity from the side opening C5 and thus affects the accuracy rate of the analysis result. Of course, the liquid guiding structure 4 can also be independently formed and then assembled on the cup body 1. And the liquid guiding structure 4 itself can be made in a split manner and then spliced into a whole. In this way, the processing precision control difficulty of the installation holes on the liquid guiding structure 4 that cooperate with the cup body 1 can be reduced. The split liquid guiding structure 4 can be easily and tightly connected to the outer wall surface of the cup body 1 through a bonding form, avoiding the leakage phenomenon caused by the fitting gap between the liquid guiding structure 4 and the outer wall surface of the cup body 1 due to the machining precision error of the installation holes on the liquid guiding structure 4.

[0056] Specifically, the liquid guiding structure 4 includes a liquid guiding plate 41 and two baffle plates 42.

[0057] The liquid guide plate 41 is in the shape of a flat plate and is connected around the outer wall surface of the cup body 1. The upper surface of the liquid guide plate 41 is perpendicular to the axis of the cup body 1. From Figure 2 As can be seen, the liquid guide plate 41 is snapped into the slot C6 on the fixed seat C1, and the bottom of the liquid guide plate 41 abuts against the bottom of the slot C6. In this way, it is possible to prevent the liquid guide structure 4 and the cup body 1 from tilting, so that the cup body 1 can better maintain a vertical arrangement state, and the reaction liquid in the cup body 1 is not likely to overflow from the cup mouth. There is also an installation hole (not labeled) on the top of the fixed seat C1 on one side of the slot C6. The edge of the installation cavity is connected with a pressing member C3, and a part of the pressing member C3 presses above the liquid guide structure 4. In this embodiment, the pressing member C3 is a screw. The structural design that the pressing member C3 presses above the liquid guide structure 4 can better fix the upper part of the reaction cup C0 and improve the stability of the reaction cup C0.

[0058] Two baffle plates 42 are connected to both sides of the liquid guide plate 41 and extend from the liquid guide plate 41 towards the cup mouth 10. The liquid guide groove formed by enclosing the two baffle plates 42 above the liquid guide plate 41 is the liquid guide channel 44. There is a notch on one of the baffle plates 42. The reagent inlet tube 111 is stuck in the notch. For the design in which the liquid guide structure 4 and the cup body 1 are separately formed, it is possible to prevent the liquid guide structure 4 from rotating relative to the cup body 1 under the action of an external force, thereby destroying the sealing connection performance between the liquid guide structure 4 and the cup body 1. The liquid guide structure 4 further includes three reinforcing plates 43. The bottom of each reinforcing plate 43 is connected to the liquid guide plate 41. One of the reinforcing plates 43 is perpendicular to the baffle plate 42, with one end connected to the cup body 1 and the other end connected to the baffle plate 42. The other two reinforcing plates 43 are parallel to the baffle plate 42, with one end being a free end and the other end connected to the cup body 1. The setting of the reinforcing plates 43 can improve the strength of the liquid guide structure 4. In addition, the number of the baffle plates 42 can also be three, four, or even more, which can be set according to actual needs and will not be specifically limited here.

[0059] The working process of the blood reaction analyzer in this embodiment is introduced below:

[0060] The sampler G takes a blood sample and sends the blood sample into the reaction cup C0;

[0061] Reagents are added into the reaction and optical detection section 12 through the reagent filling pipeline 52 and the reagent inlet tube 111;

[0062] The power device D sucks the diluent into the first pipeline 61 along the second pipeline 62;

[0063] Disconnect the second pipeline 62;

[0064] The diluent in the first pipeline 61 is successively passed through the main pipeline 63 and the liquid inlet pipeline 632 into the buffer cavity F by the power device D. The diluent gradually fills the space in the buffer cavity F, and the air in the buffer cavity F is pressed into the reaction cup C0. The air forms bubble turbulence in the reaction cup C0 to mix the reaction liquid. The bubbles overflow from the cup mouth 10 out of the reaction cup C0. Compared with the design of mixing the reaction liquid by repeatedly sucking and discharging the liquid, the surging of the reaction liquid during the mixing process is not large, so that the reaction liquid can be prevented from surging into the reagent inlet and the reagent inlet pipe 111. In this embodiment, the power device D can be a syringe or other structures or devices such as an air pump;

[0065] The power device D is turned off, and the detection light is emitted from the light source assembly C2 to the light transmissive member 2. The detection light passes through the reaction liquid and then passes out of the other light transmissive member 2, and is received and analyzed by the light receiving and analyzing assembly C4 to obtain the blood sample analysis result;

[0066] The drain control valve (not shown) on the drain tail pipe 65 is opened, and the reaction liquid is discharged through the transition part 131, the discharge pipe 132, the discharge port 14, the buffer cavity F, and the drain tail pipe 65.

[0067] Obviously, the above embodiments are only examples for clear illustration and not limitations on the implementation manners. For those of ordinary skill in the art, other different forms of changes or modifications can be made based on the above description. It is not necessary and impossible to list all the implementation manners here. And the obvious changes or modifications derived therefrom are still within the protection scope of the present invention.

Claims

1. A blood reaction analyzer, characterized in that: include: Blood routine test component (B); A specific protein detection component (C) comprises a cup body (1), the upper end of the cup body (1) is an open cup mouth (10), and the lower end is a discharge port (14), the cup body (1) comprises a filling section (11) and a reaction light detection section (12) arranged in sequence from the cup mouth (10) to the discharge port (14), the reaction light detection section (12) is a region where a biological sample and a reagent react, the outer wall of the filling section (11) is connected to a reagent inlet pipe (111), and the reagent inlet pipe (111) is suitable for connecting to a reagent filling pipeline (52) for injecting a reagent.

2. The blood reaction analyzer according to claim 1, characterized in that: The opening of the reagent inlet tube (111) is connected to a reducer interface tube (51), and at least two interfaces are provided on one end of the reducer interface tube (51) facing away from the cup body (1), one of the interfaces is connected to the flushing pipeline (631), and the other interfaces are connected to the reagent filling pipeline (52).

3. The blood reaction analyzer according to claim 2, characterized in that: At least two reagent filling branch pipelines (521) are provided on one end of the reagent filling pipeline (52) facing away from the cup body (1).

4. The blood reaction analyzer according to claim 3, characterized in that: The diameter of the variable diameter interface pipe (51) is larger than the diameter of any of the reagent filling branch pipelines (521).

5. The blood reaction analyzer according to claim 2, characterized in that: The flushing pipeline (631) is provided with a flushing pipeline control valve (6310) for controlling the on-off of the flushing pipeline (631).

6. The blood reaction analyzer according to claim 1, characterized in that: The reagent inlet tube (111) is arranged at an angle, and the position of one end of the reagent inlet tube (111) connected to the reagent filling pipeline (52) is higher than the position of one end of the reagent inlet tube (111) connected to the reaction optical detection section (12).

7. The blood reaction analyzer according to claim 1, characterized in that: The specific protein detection component (C) further comprises: A fixing seat (C1) is provided with a mounting cavity having a top opening; A light source assembly (C2) is mounted on the fixing seat (C1) and is located on the light incident surface of the cup body (1), and is suitable for emitting detection light to the light incident surface of the cup body (1); The light receiving and analyzing component (C4) is mounted on the fixing seat (C1) and is located on the light emitting surface side of the cup body (1), and is suitable for receiving the detection light emitted from the light emitting surface of the cup body (1), wherein the light emitting surface is arranged opposite to the light incident surface.

8. The blood reaction analyzer according to claim 7, characterized in that: The outer wall surface of the cup body (1) is surrounded and connected with a liquid guide structure (4), and a liquid guide channel (44) communicating with the outer wall surface of the cup body (1) is formed on the liquid guide structure (4). The liquid guide structure (4) is located at the top opening of the installation cavity, and the reaction liquid overflowing from the cup mouth (10) is suitable for being discharged outward through the liquid guide channel (44).

9. A blood reaction analyzer, characterized in that: include: Blood routine test component (B); A specific protein detection component (C) comprises a cup body (1), the upper end of the cup body (1) is an open cup mouth (10), and the lower end is a discharge port (14), the cup body (1) comprises a filling section (11) and a reaction light detection section (12) arranged in sequence from the cup mouth (10) to the discharge port (14), the reaction light detection section (12) is a region where a biological sample and a reagent react, the outer wall of the filling section (11) is connected to a reagent inlet pipe (111), the reagent inlet pipe (111) is suitable for connecting to a reagent filling pipeline (52) for injecting a reagent, discharging a reaction liquid through the discharge port (14), and injecting bubbles into a reaction cup (C0) from a power device (D) through the discharge port (14) to mix the reaction liquid.

10. The blood reaction analyzer according to claim 9, characterized in that: The specific protein detection component (C) also includes a three-way valve (E) and a buffer chamber (F); the power device (D) is connected to the first opening of the three-way valve (E) through a first pipeline (61); the second opening and the third opening of the three-way valve (E) are respectively connected to the diluent through a second pipeline (62), and are connected to the reaction optical detection section (12) through a flushing pipeline (631).

11. A method for mixing a reaction solution, based on the blood reaction analyzer according to any one of claims 9 or 10, characterized in that: The steps include: The power device (D) draws the diluent along the second pipeline (62), and the diluent enters the first pipeline (61); Disconnecting the second pipeline (62); The power device (D) delivers the diluent in the first pipeline (61) into the buffer chamber (F), presses the air in the buffer chamber (F) into the reaction cup (C0) to form bubbles, and the bubbles form turbulence to mix the reaction liquid.

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