Centrifugal microfluidic biochemical analysis chip
By densely distributing reaction detection grooves on a centrifugal microfluidic chip and employing a groove and reflective surface design, the problem of not being able to complete multiple detections at once in existing technologies has been solved, achieving efficient and low-cost biological data acquisition.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- TIANJIN MNCHIP TECH CO LTD
- Filing Date
- 2025-03-25
- Publication Date
- 2026-04-10
AI Technical Summary
Existing centrifugal microfluidic chips can only perform two or more analysis operations in biological detection, and cannot complete more than 30 tests at once, resulting in increased time consumption and costs.
By improving the marker positioning structure, the reaction detection slots are more densely distributed around the chip substrate, increasing the number of reaction detection slots. The use of grooves and reflective surfaces ensures accurate positioning, accurate reception of optical signals, and reduces the space occupied by the marker positioning structure.
This enables more testing items to be completed on the same chip, reducing testing costs and improving testing efficiency and accuracy.
Smart Images
Figure CN224100736U_ABST
Abstract
Description
Technical Field
[0001] This utility model relates to the technical field of microfluidic detection, specifically to a centrifugal microfluidic biochemical analysis chip. Background Technology
[0002] Microfluidic chips are a hot topic in the development of micro total analytical systems. They integrate sample detection for biological, chemical, and medical analytical processes onto a tiny chip. Microfluidic chips offer advantages such as controllable liquid flow, minimal sample and reagent consumption, and high analysis speed. They can simultaneously analyze hundreds of samples in minutes or even less, and can perform online sample pretreatment and analysis.
[0003] The basic principle of centrifugal microfluidic chips for biological sample detection is to use centrifugation to introduce liquid samples (usually blood or urine) into reaction detection cells located at the edge of the chip. Different reaction detection cells are pre-filled with different reagents. After the sample reacts with the reagents in the reaction detection cells, it undergoes optical analysis to obtain various required biological data. During this process, precise positioning and labeling of the reaction detection cells are necessary so that the operator can obtain the corresponding results. Conventional centrifugal microfluidic chips, such as... Figure 1 As shown, the reaction detection slots are arranged along the circumference of the chip. They are positioned using a physical marking method. A reflective signal mechanism corresponding to the detection slot is set. The detected light signal marks the position of the corresponding detection slot. The physical marking positioning structure is spaced apart from the reaction detection slots and corresponds one-to-one. Generally, 28 to 30 reaction detection slots can be set.
[0004] However, in practice, only 21 of the 30 reaction detection cells are used for biological sample index analysis, while the remaining cells are used for waste liquid recovery, etc. With the development of medicine, more than 30 indicators can be obtained from human fluid samples through optical analysis. For certain diseases, doctors and patients hope to be able to analyze all the required more than 30 indicators at once, so that doctors can quickly obtain relevant data and make a comprehensive judgment on the condition.
[0005] Due to the limitations of the existing microfluidic chip structure, the comprehensive analysis required above can only be performed twice or more, which is not only time-consuming but also costly. Utility Model Content
[0006] This invention provides a centrifugal microfluidic biochemical analysis chip. To address the aforementioned problems in existing technologies, the design of the marking and positioning structure is improved, resulting in a denser distribution of reaction detection slots around the chip substrate. This allows for the addition of more reaction detection slots on a single chip, enabling the acquisition of as much detection data as possible in a single test. It also facilitates the design of chips capable of performing parallel detection of multiple parameters. Specific implementation details are as follows:
[0007] A centrifugal microfluidic biochemical analysis chip comprises a chip substrate;
[0008] A liquid adding groove is arranged at a position adjacent to the central axis of the chip substrate and is used for sample injection;
[0009] A plurality of reaction detection grooves are arranged at positions away from the rotation center of the chip substrate in the circumferential direction and are used for sample detection;
[0010] A flow guide channel is connected between the liquid adding groove and the reaction detection groove and is used for guiding the liquid sample into the reaction detection groove during centrifugal operation;
[0011] A positioning structure is arranged corresponding to the reaction detection groove and is used for positioning the reaction detection groove, wherein the positioning structure comprises a groove and a reflecting surface arranged on the groove, and the projection width of the reflecting surface along the thickness direction of the chip is the same as the width of the groove.
[0012] As a further scheme of the utility model, a plurality of grooves are arranged at the distal end of the chip substrate, and the grooves are arranged between adjacent reaction detection grooves.
[0013] As a further scheme of the utility model, a plurality of grooves are arranged at equal intervals in the circumferential direction of the chip substrate, and the reaction detection grooves are arranged between adjacent grooves.
[0014] As a further scheme of the utility model, the groove is opened in the axial direction of the chip substrate, and the cross-sectional shape of the groove perpendicular to the opening direction is the same as the projection cross-sectional shape of the reflecting surface at the mounting position.
[0015] As a further scheme of the utility model, the width of the reflecting surface is 0.5-1.3mm.
[0016] As a further scheme of the utility model, the width of one of the reflecting surfaces is greater than the width of the other reflecting surfaces.
[0017] As a further scheme of the utility model, the angle between the reflecting surface and the bottom surface or the top surface of the chip substrate is α, and the angle α is arranged to be between 40° and 50°.
[0018] As a further scheme of the utility model, the angle between the reflecting surface and the bottom surface or the top surface of the chip substrate decreases with the decrease of the groove depth.
[0019] As a further scheme of the utility model, the position corresponding to the reaction detection groove on the bottom surface of the chip substrate is provided with a non-closed groove, the projection of the reaction detection groove in the thickness direction is located in the projection of the groove, and the open end of the non-closed groove extends to the edge of the chip substrate.
[0020] Due to the adoption of the above technical scheme, the beneficial technical effects of the utility model are:
[0021] The utility model discloses a recess width and reflection face width are designed as the same, can control the size of mark positioning structure as far as possible, make reaction detection groove distribute more closely on the chip substrate periphery, increase more reaction detection groove, complete as far as possible more detection project on the same chip, reach once detection can obtain as far as possible comprehensive biological data, save detection time, reduce detection cost. BRIEF DESCRIPTION OF DRAWINGS
[0022] Figure 1 It is the top view of centrifugal microfluidic biochemical analysis chip of prior art;
[0023] Figure 2 It is the top view of centrifugal microfluidic biochemical analysis chip of prior art;
[0024] Figure 3 It is the top view of centrifugal microfluidic biochemical analysis chip of prior art; Figure 1 It is the structure enlarged view of part A in the utility model;
[0025] Figure 4 It is the top view of centrifugal microfluidic biochemical analysis chip of prior art;
[0026] Figure 5 It is the top view of centrifugal microfluidic biochemical analysis chip of prior art; Figure 3 It is the structure enlarged view of part B in the utility model.
[0027] BRIEF DESCRIPTION OF DRAWINGS
[0028] 1, chip substrate, 11, liquid adding groove, 12, reaction detection groove, 13, positioning structure, 14, starting positioning structure, 131, recess, 132, reflection face. DETAILED DESCRIPTION
[0029] The utility model specific implementation is described below in combination with the drawings and examples:
[0030] It should be noted that the structure, proportion, size etc. in the drawings attached to the present specification are merely used to cooperate with the content disclosed in the specification, so as to be understood and read by those skilled in the art, and are not used to limit the implementation conditions of the utility model, any modification of structure, change of proportion relationship or adjustment of size, as long as it does not affect the effect and purpose that the utility model can produce, should still fall within the range covered by the technical content disclosed in the utility model.
[0031] Meanwhile, the terms such as "upper", "lower", "left", "right", "middle" and "one" used in this specification are only for clarity of description and are not intended to limit the scope of implementation of this utility model. Changes or adjustments to their relative relationships, without substantially altering the technical content, should also be considered as within the scope of implementation of this utility model.
[0032] In centrifugal microfluidic biochemical analysis chips, centrifugal force first propels the sample from a liquid addition tank near the center of rotation to a pre-addition reagent reaction detection tank, followed by optical detection. Marking and positioning the pre-addition reagent reaction detection tanks is crucial to determining which reagent is added to each tank and what test is being performed. In existing technologies, a marking and positioning reflective surface is typically placed near each reaction detection tank during the chip substrate injection molding process, integrally molded with the tank. When the detection light hits the reflective surface and generates a reflected signal, the position and sequence of the corresponding reaction detection tanks can be marked and positioned. Due to process limitations, this reflective surface is usually placed within a recess, the lateral dimension of which is much larger than the reflective surface itself. This recess occupies circumferential space on the chip substrate. When both the reflective surface and the reaction detection tanks are arranged circumferentially, it limits the number of reaction detection tanks that can be used. Figure 1 In the analysis chip shown, due to the wide groove, the reaction detection slots can only be set to 29, of which only 20 are used for optical analysis to obtain data. When more than 30 detection items need to be performed, two chips must be used for two analysis operations, which takes a long time or is costly.
[0033] To address the above problems, this invention provides a centrifugal microfluidic biochemical analysis chip, such as... Figure 2 As shown, the chip substrate includes a chip substrate 1; a liquid injection tank 11, located on the top surface of the chip substrate 1 near the central axis, for sample injection; multiple reaction detection tanks 12, arranged circumferentially on the chip substrate 1 away from the rotation center, for sample detection; a flow channel connecting the liquid injection tank 11 and the reaction detection tanks 12, for introducing liquid samples into the reaction detection tanks 12 during centrifugation; and a positioning structure 13, corresponding to the reaction detection tanks 12, for detecting and positioning the reaction detection tanks 12. The positioning structure 13 includes a groove 131 and a reflective surface 132 disposed on the groove 131, wherein the projection width of the reflective surface 132 in the chip thickness direction is the same as the width of the groove 131.
[0034] In this embodiment, the width of the reflecting surface 132 in the direction of the chip surface projection is the same as the width of the groove 131, eliminating the invalid part of the groove 131 in the width direction in the prior art, which can reduce the occupied space of the mark positioning structure 13 as much as possible, make the distribution of the reaction detection groove 12 on the chip substrate 1 more compact, increase more reaction detection grooves 12, store more samples on the same chip, or meet the needs of more types of detection items, thereby reducing the detection cost; in addition, from the projection direction of the chip thickness, the reflecting surface 132 completely coincides with the groove 131, which ensures that the reflecting surface 132 accurately receives the light source, avoids the problem of signal loss or measurement error, and helps to improve the detection accuracy.
[0035] Specifically, a plurality of grooves 131 are arranged at the far end of the chip substrate 1, and the grooves 131 are arranged between adjacent reaction detection grooves 12. The groove 131 is arranged along the thickness direction of the chip substrate 1, and the reflecting surface 132 is arranged on the groove bottom of the groove 131. In specific applications, the chip substrate 1 is accurately positioned by the reflecting surface 132 and then subjected to in-situ optical detection.
[0036] Specifically, a plurality of said grooves 131 are arranged at equal intervals along the circumferential direction of the chip substrate 1, and said reaction detection grooves 12 are arranged between adjacent said grooves 131. The groove 131 corresponds to the reaction detection groove 12 one by one, and the sample input into the reaction detection groove 12 can be accurately positioned according to the reflecting surface 132 of the groove 131, and the required reagent is added to react with the sample in the reaction detection groove 12 to obtain the detection result. The number of grooves 131 and reaction detection grooves 12 in this embodiment can be selected according to actual conditions.
[0037] Specifically, as shown in the partial enlarged view of the reflecting surface 132, Figure 3 The groove 131 is opened along the thickness direction of the chip substrate 1, and the cross-sectional shape of the groove 131 perpendicular to the opening direction is the same as the projection cross-sectional shape of the reflecting surface 132 at its mounting position (in the chip thickness direction). In this embodiment, the width of the groove 131 is consistent with the width of the reflecting surface 132. The width of the reflecting surface 132 is e, and since the reflecting surface 132 is located on the groove bottom of the groove 131, the width of the groove 131 is accordingly e. Preferably, the width of the reflecting surface 132 is set to be between 0.5-1.3mm. In a preferred embodiment, the width of the groove 131 is set to 1mm, and correspondingly, the width of the reflecting surface 132 e is set to 1mm, both of which have the same width, which can make the reaction detection groove 12 and the groove 131 more compact, thereby increasing the number of reaction detection grooves 12, and further increasing the number of chip substrates 1 containing the to-be-tested items. In this embodiment, the number of reaction detection grooves 12 can be set to 41, of which 33 can be used for optical analysis and detection, and 33 detection items can be completed at a time in one chip, which fully meets the current demand for personal biological sample index analysis.
[0038] As a preferred embodiment of the present application, one of the reflection surfaces 132 is provided as a starting positioning structure 14, which is used as a marker for positioning the overall position of the chip substrate 1. The width of the starting positioning structure 14 is 2 mm. Starting from the clockwise (or counterclockwise) direction of the chip substrate 1, each reflection surface is sequentially labeled. When one of the reflection surfaces 132 receives a light path, the corresponding reaction detection groove 12 can be quickly identified by identifying the label, so that the identification of the detection result is more efficient and fast.
[0039] Specifically, as shown in the partial enlarged view of Figure 4 and Figure 5 , the angle between the reflection surface 132 and the bottom surface or the top surface of the chip substrate 1 is α, and the angle α is set to be between 40° and 50°. Preferably, the angle α is set to be 45°, so that the reflection surface 132 effectively receives the light path, accurately concentrates the light intensity in the area of the reflection surface 132, and ensures the effective use of the light signal.
[0040] As another embodiment of the present application, the angle between the reflection surface 132 and the bottom surface or the top surface of the chip substrate 1 decreases with the decrease of the groove depth of the groove 131. For example, when the groove depth of the groove 131 is set to be 5 mm, the angle α between the reflection surface 132 and the bottom surface or the top surface of the chip substrate 1 is correspondingly set to be 45°; when the groove depth of the groove 131 is set to be 4 mm, the angle α between the reflection surface 132 and the bottom surface or the top surface of the chip substrate 1 is correspondingly set to be 40°, so as to ensure that the reflection surface 132 vertically receives the light source signal as much as possible.
[0041] Specifically, the groove 131 is opened from the top surface of the chip substrate 1 or the bottom surface of the chip substrate 1, and the reflection surface 132 is arranged to face the direction of the rotation center axis of the chip substrate 1. In this embodiment, the groove 131 is opened along the bottom surface of the chip substrate 1 to the top surface, the reflection surface 132 faces the top surface, and after the rotation of the chip substrate 1, the sample in the liquid adding groove 11 is output to the corresponding reaction detection groove 12 by using the centrifugal force, and the in-situ optical detection is performed after the accurate positioning by using the reflection surface 132.
[0042] In another embodiment, the groove 131 has a trapezoidal structure. Preferably, the groove 131 has a right-angled trapezoidal structure along the axial section, and the reflection surface 132 is arranged on the opposite sides of the right angles of the right-angled trapezoidal structure, so that the groove 131 has an inclined surface on the groove bottom surface.
[0043] In one embodiment, the bottom surface of the chip opposite the reaction detection groove 12 is provided with an open groove, the open end of which extends to the edge of the chip. For example, the open groove is provided in the form of a U-shaped groove, as viewed from the bottom surface of the chip, the light transmission area of the reaction detection groove 12 is located in the closed end of the U-shaped groove, and the open end of the U-shaped groove extends to the edge of the chip, thereby forming an open groove structure. This structure design can guide the flow direction of the injection molding liquid during the injection molding process of the chip, thereby avoiding the merging point of multiple injection molding liquids from appearing in the light transmission area of the reaction detection groove 12 to form a weld mark, which affects the optical detection result. The U-shaped groove is only one structure form in this example, and under the purpose of guiding the flow direction of the injection molding liquid, those skilled in the art can set the open groove in various shapes as appropriate. In addition, the open groove can correspond to the reaction detection groove 12 one by one, or can be selectively provided on the bottom surface of the corresponding position of the reaction detection groove 12, and those skilled in the art can design according to actual needs.
[0044] The working principle of the utility model is that the sample is injected into the liquid adding groove 11, and then the sample in the liquid adding groove 11 is injected into the reaction detection groove 12 through a guide channel by means of increasing the rotating speed, for example. Before detection, the reaction detection groove 12 is positioned by the positioning structure 13, the marking position of each reaction detection groove 12 is completed, corresponding to the required detection item, and finally the detection operation is carried out. The guide channel in the present specification refers to the structure through which the sample flows from the liquid adding groove 11 to the reaction detection groove 12 under the action of centrifugal force in the sample detection process of the prior art centrifugal microfluidic chip, including but not limited to various grooves and capillary channels, and the present specification will not be repeated.
[0045] Many other changes and modifications can be made without departing from the spirit and scope of the utility model. It should be understood that the utility model is not limited to the specific embodiments, and the scope of the utility model is defined by the appended claims.
Claims
1. A centrifugal microfluidic biochemical analysis chip, characterized by, The chip substrate (1) comprises: a liquid adding groove (11) arranged at a position adjacent to the center axis of the chip substrate (1) and used for sample injection; a plurality of reaction detection grooves (12) arranged at positions away from the rotation center of the chip substrate (1) in the circumferential direction and used for sample detection; a flow guide channel connecting the liquid adding groove (11) and the reaction detection groove (12) and used for guiding the liquid sample into the reaction detection groove (12) during centrifugation; a positioning structure (13) arranged corresponding to the reaction detection groove (12) and used for positioning the reaction detection groove (12), wherein the positioning structure (13) comprises a groove (131) and a reflecting surface (132) arranged on the groove (131), and the projection width of the reflecting surface (132) in the thickness direction of the chip is the same as the width of the groove (131).
2. The centrifugal microfluidic biochemical analysis chip according to claim 1, wherein, A plurality of the grooves (131) are uniformly arranged at the far end of the chip substrate (1), and the grooves (131) are arranged between adjacent reaction detection grooves (12).
3. The centrifugal microfluidic biochemical analysis chip according to claim 2, wherein, A plurality of the grooves (131) are arranged at equal intervals in the circumferential direction of the chip substrate (1), and the reaction detection grooves (12) are arranged between adjacent grooves (131).
4. The centrifugal microfluidic biochemical analysis chip according to claim 1, wherein, The groove (131) is opened in the axial direction of the chip substrate (1), and the cross-sectional shape of the groove (131) perpendicular to the opening direction is the same as the projection cross-sectional shape of the reflecting surface (132) at the mounting position.
5. The centrifugal microfluidic biochemical analysis chip of claim 1, wherein, The width of the reflecting surface (132) is 0.5-1.3mm.
6. The centrifugal microfluidic biochemical analysis chip according to claim 5, wherein, The width of one of the reflecting surfaces (132) is greater than the width of the other reflecting surfaces (132).
7. The centrifugal microfluidic biochemical analysis chip of claim 1, wherein, The angle between the reflecting surface (132) and the bottom surface or top surface of the chip substrate (1) is α, and the angle α is arranged to be between 40° and 50°.
8. The centrifugal microfluidic biochemical analysis chip of claim 1, wherein, The angle between the reflecting surface (132) and the bottom surface or top surface of the chip substrate (1) decreases with the decrease of the groove depth of the groove (131).
9. The centrifugal microfluidic biochemical analysis chip of claim 1, wherein, The bottom surface of the chip substrate (1) is provided with a non-closed groove at a position corresponding to the reaction detection groove (12), the reaction detection groove (12) is projected in the projection of the groove in the thickness direction, and the open end of the non-closed groove extends to the edge of the chip substrate (1).