WO2013007028A1 - 对基于微流控芯片的检测系统进行自校准的方法及系统 - Google Patents
对基于微流控芯片的检测系统进行自校准的方法及系统 Download PDFInfo
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- WO2013007028A1 WO2013007028A1 PCT/CN2011/077131 CN2011077131W WO2013007028A1 WO 2013007028 A1 WO2013007028 A1 WO 2013007028A1 CN 2011077131 W CN2011077131 W CN 2011077131W WO 2013007028 A1 WO2013007028 A1 WO 2013007028A1
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- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
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- B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
- B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
- B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
- B01L3/502769—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by multiphase flow arrangements
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- G01N15/1459—Optical investigation techniques, e.g. flow cytometry without spatial resolution of the texture or inner structure of the particle, e.g. processing of pulse signals the analysis being performed on a sample stream
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Definitions
- the present invention relates to a self-calibration method and system, and more particularly to a method and system for self-calibration of a microfluidic chip based detection system.
- the microfluidic chip analysis uses the chip as the operating platform.
- based on analytical chemistry relying on micro-electromechanical processing technology, micro-pipeline network as the structural feature, life science as the main application object, is the focus of the development of the current micro-analysis system. Its goal is to integrate the entire laboratory function, including sampling, dilution, reagent addition, reaction, separation, detection, etc. on the microchip, and can be used multiple times.
- the microfluidic chip has the characteristics of controllable liquid flow, minimal consumption of samples and reagents, and an increase in analysis speed by hundreds of times. It can perform simultaneous analysis of hundreds of samples in a few minutes or even less. And the sample pretreatment and analysis process can be realized online.
- the microfluidic controller and detector system includes a fluidic chip, the chip including at least two intersecting channels and a detection zone, the fluid guiding system comprising an electrical interface in electrical contact with at least two intersecting channels, an optical module having an objective lens placed adjacent the detection zone And a control system coupled to the optical module and adapted to receive and analyze optical module data.
- the electrical interface typically includes an electrode in electrical contact with the intersecting channel and coupled to the electrode channel for providing electrical input to the electrode.
- the reference channel corrects the electrode channel.
- the method is complicated to operate and is not conducive to the practical application of the microfluidic chip.
- the technical problem to be solved by the present invention is that the above-mentioned operations for the prior art are complicated, which is not conducive to practical application defects, and provides a method for self-calibration of a microfluidic chip-based detection system that is easy to operate and beneficial to practical applications. system.
- the technical solution adopted by the present invention to solve the technical problem thereof is to construct a method for self-calibration of a detection system based on a microfluidic chip, which is characterized in that it comprises the following steps:
- the detection channel of the detection zone allows only one of the reference microbeads or the particles of the analysis sample to pass at a time, and the sensor of the detection zone detects the signal generated by the reference microbead or the analysis sample;
- the signal generated by the reference bead is significantly different from the signal generated by the analysis sample. ; described in step S1'
- the reference microbeads are separated from the analytical sample by air or separated by a liquid, and the reference microbeads are built into the microfluidic system.
- the sensors in the detection area include electrical sensors and optical sensors.
- the optical sensor detects at least one of forward scatter, side scatter, and fluorescent signal.
- the electrical sensor detects at least one of a capacitance and a direct current impedance, a radio frequency impedance, and a low frequency impedance signal.
- the reference microbead comprises at least one particle having a known volume shape or having known optical or electrical properties.
- the size of the reference microbead is fixed, and the widest part of the microbead has a length ranging from 10 nm to 1000.
- Um the shape of the reference datum bead is spherical, square or triangular.
- the reference microbead is solid, hollow or a particle containing a specific fluorescent substance.
- the reference microbead is made of glass, latex, silica gel, agar, resin, plastic, ceramic or metal.
- a system for self-calibrating a microfluidic chip-based detection system including a reference bead and a microfluidic chip, is also provided.
- the reference microbead comprises at least one particle having a known size or having known optical or electrical properties, and the reference microbead is mixed with the analysis sample and detected by the microfluidic chip. a region, and when passing through the detection zone, the electrical or optical signal generated by the reference bead is significantly different from the electrical or optical signal produced by the analytical sample; or the reference bead is built into the microfluidic system Separating from the analysis sample, respectively, passing through the detection area of the microfluidic chip,
- the detection channel of the microfluidic chip allows only one of the reference microbeads or the particles of the analysis sample to pass at a time
- the sensor of the microfluidic chip comprises an electrical sensor and an optical sensor, respectively detecting the characteristic reference microbeads and Analyzing an optical characteristic or an electrical characteristic of the sample, and comparing the detection result with a known optical characteristic or electrical characteristic of the reference microbead, determining a calibration coefficient, and self-calibrating the microfluidic chip-based detection system, thereby The test results of the analytical sample are calibrated.
- the method and system for self-calibration of the microfluidic chip-based detection system provided by the invention have the following beneficial effects: the operation is simple, and the practical application can make the microfluidic chip more accurate for detecting the sample.
- FIG. 1 is a schematic diagram of a self-calibration process of a first embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention
- FIG. 2 is a schematic diagram of a self-calibration result of a first embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention
- FIG. 3 is a schematic diagram of a self-calibration process of a second embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention
- FIG. 4 is a schematic diagram of a self-calibration result of a second embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention
- FIG. 5 is a schematic diagram showing the self-calibration result of the third embodiment of the method for self-calibration of a microfluidic chip-based detection system according to the present invention.
- a microfluidic analysis product refers to an analytical device for detecting and analyzing biological or chemical samples, which forms micro-scale microchannels on a chip by techniques such as micro-etching to supply or mix a plurality of sample solutions and reagents, thereby enabling the liquid to The reaction is carried out in the channel and signal detection is performed in the detection zone.
- the detection object it can be generally divided into a DNA chip, an RNA chip, a protein chip, and a cell chip.
- cell chips are commonly used to analyze yeast cells, sperm cells, blood cells, and tumor cells.
- the present invention provides a method for self-calibration of a microfluidic chip-based detection system, the method comprising adding a reference microbead of fixed size, shape or particle nature to a solution of a microfluid, the reference microbead passing through the detection zone
- the generated optical signal or electrical signal can automatically calibrate the size of the detection hole to automatically correct the detection signal of the analysis sample.
- the method provided by the invention can self-calibrate the microfluid analysis product, especially the disposable microfluidic product, can effectively avoid the adverse influence on the detection signal caused by the inconsistent detection area size generated by the manufacturing process, and increase the quantity between the batch products. Consistency is conducive to large-scale practical application of microfluidic products.
- a cell chip is taken as an example to describe in detail a method for self-calibration of a detection system based on a microfluidic chip.
- FIG. 1 is a schematic diagram of a self-calibration process of a first embodiment of a self-calibration method for a microfluidic chip-based detection system according to the present invention.
- 10 um will be The latex reference beads are built into the microfluidic system detection zone and are insulated by air at both ends.
- the latex reference microbeads first passed through the detection zone.
- the detection zone is shown in Figure 1.
- Two detection electrodes are provided to measure the impedance of the passed latex reference beads.
- the direction indicated by the arrow is the flow direction of the latex reference microbeads.
- the yeast cell solution was then added and a similar method was used for signal detection. The same sample was used to detect with two microfluidic chips, and the signals of 100 yeast cells and reference microbeads were respectively averaged.
- FIG. 2 is a schematic diagram of a self-calibration result of a first embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention.
- a is the voltage of the latex-referenced microbeads of the chip 1 which is not self-calibrated;
- b is the voltage of the yeast cell which is not self-calibrated by the chip 1;
- c is the chip 2 which is not self-calibrated to detect the latex standard
- d is the voltage of the yeast cell which is not self-calibrated by the chip 2;
- e is the voltage of the yeast cell detected by the self-calibrated chip 1; and
- f is the voltage of the yeast cell detected by the self-calibrating chip 2.
- the above latex-based microbeads are all of the same type, and the yeast cells are all of the same type.
- the measurement signals of the two microfluidic chips on the yeast cells are quite different, but after the signal correction by the same latex reference microbeads, the measurement results of the yeast cells are basically the same, indicating that the self-calibration method of the microfluid analysis product provided by the invention can It effectively reduces the adverse effect on the detection signal due to the inconsistent size of the detection area caused by the manufacturing process, and increases the consistency between the batch products.
- the method is convenient to operate, does not need to increase the complexity of microfluidic product design, and is beneficial to large-scale practical application of microfluidic products.
- Example 2 Self-calibration method for sperm analysis microfluidic chip
- FIG. 3 is a schematic diagram of a self-calibration process of a second embodiment of a method for self-calibrating a detection area of a microfluidic chip according to the present invention.
- the sperm analysis microfluidic chip is provided with a detection hole in the detection channel, and has a pair of electrode sensors built therein. Since the sperm itself has low conductivity, when the sperm passes through the detection hole, the liquid at the detection hole is detected. The low frequency conductivity drops, and a pair of electrodes in the detection hole are detected as voltage pulses and this impedance change is recorded.
- This principle is the Coulter principle, according to which the sperm in a certain time and a certain area can be counted, and then the number of sperm and the exercise ability parameter are converted.
- the um-sized reference beads are mixed and added together to the microfluidic analysis chip inlet, and the sperm and the reference microbeads pass through the microchannel to enter the detection hole.
- the principle of counting the particles by the Coulter principle when the sperm and the reference microbead individually pass through the detection hole, respective impedance signals are generated, and the area of the peak is selected for impedance data analysis, because the sperm and the reference microbead are in size and shape. There are differences, so the resulting impedance signals are different and easy to distinguish.
- the average impedance signal theoretically generated by the reference microbead through the detection zone is V
- the average impedance signal is measured as Vm
- the theoretical number of reference microbeads is N
- the total amount of measurement reference microbeads is Nc.
- the average impedance signal measured by the sperm is Vs
- the total number of sperm measurements is Ns.
- the corrected impedance signal of the sperm is Vs ⁇ Vm/V
- the corrected number of sperm is Ns ⁇ Nc/N.
- FIG. 4 is a schematic diagram of a self-calibration result of a second embodiment of a method for self-calibration of a microfluidic chip-based detection system according to the present invention.
- g is the signal curve of the reference bead
- h is the signal curve of the sperm.
- Blood counts are among the most common blood tests in the medical field, and abnormal increases or decreases in counts may indicate the presence of many diseases that provide an overview of the overall health of the patient.
- the basic flow of blood cell count is that the blood is first diluted by the isotonic diluent, and the cells suspended in the diluent are arranged in a single column through a flow detector. At this time, the cells are in a narrow focused light path, each blood cell. When passing through, a beam of light is blocked, and a certain number of cells continuously interrupt the beam, causing the detector to detect the number of times the light is blocked per unit time, thereby calculating the number of cells.
- Light scattering can also determine the size and morphology of each cell based on the angle of scattering produced by each cell as it passes.
- the forward scattered light (FSC) and side scattered light (SSC) generated by scattering can be used to detect the cell size and the contents of the cells (nucleus and particle conditions), respectively.
- the um-sized reference beads are mixed and added to the microfluidic analysis chip inlet, and the red blood cells and the reference microbeads pass through the microchannel to enter the detection hole.
- the cells are in a narrow focused light path, and the number of cells blocked by the detector is detected by the detector to calculate the number of cells.
- the forward and lateral optical sensors detect the forward scattered light generated by the individual cells. (FSC) and side scatter light (SSC).
- FSC forward scattered light generated by the individual cells.
- SSC side scatter light
- the calibration reference bead passes through the detection aperture, it also blocks the beam from producing forward scattered light (FSC) and side scattered light (SSC) signals.
- the reference bead passes theoretically the average forward scattered light (FSC) signal to be F, the average forward scattered light signal is Fm, and the reference microbead theoretically produces an average side scattered light signal through the detection zone.
- FSC forward scattered light
- Fm forward scattered light
- Fm forward scattered light
- S side scattered light
- Nc the total amount of measurement reference beads
- the average forward scattered light signal measured by red blood cells is Fr
- the average side scattered light signal measured by red blood cells is Sr
- the total number of measured red blood cells is Nr.
- the corrected forward scattered light signal of red blood cells is Fr ⁇ Fm/F.
- the corrected side scattered light signal of the red blood cells is Sr ⁇ Sm/S, and the corrected number of red blood cells is Nr ⁇ Nc/N.
- FIG. 5 is a schematic diagram of a self-calibration result of a third embodiment of a self-calibration method for a microfluidic chip-based detection system according to the present invention.
- i shows the scattering information of the red blood cells
- j shows the scattering information of the reference microbeads.
- the electrode design method in each of the above embodiments is one of a plurality of electrode design methods, and the present invention is not limited thereto.
- the manufacturing method of the microfluidic chip for microfluidic analysis is not specifically limited.
- a PDMS can be used in combination with a slide or a silicon wafer, or a plastic microfluidic chip (PMMA) can be prepared by a hot press molding method.
- PMMA plastic microfluidic chip
- the shape of the microchannel is not specifically limited.
- the microchannel between the inlet and the detection zone may be a straight line, a circle, an ellipse, a polygon, or the like.
- the reference microbead as a calibration reagent is preferably spherical, uniform in morphology, and relatively uniform in signal.
- the material of the reference microbead is preferably silica gel, which is convenient to manufacture.
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Abstract
本发明提供了一种对基于微流控芯片的检测系统进行自校准的方法，包括以下步骤：S1，将已知特性的基准微珠与分析样品混匀后，一同进入微流控芯片的检测区；或者，S1'，将已知特性的基准微珠与分析样品隔开，分别通过微流控芯片的检测区；S2，检测区的检测通道每次仅允许一个基准微珠或分析样品的粒子通过，检测区的传感器检测基准微珠或分析样品产生的信号；S3，将基准微珠的已知特性与检测结果进行比较，确定校准系数，校准微流控芯片的检测区以及分析样品的检测结果。本发明还提供相对应的系统。实施本发明提供的方法及系统，操作简便，能够使微流控芯片对分析样品的检测更为准确。
Description
本发明涉及一种自校准的方法及系统，更具体地说，涉及一种对基于微流控芯片的检测系统进行自校准的方法及系统。
微流控芯片分析以芯片为操作平台,
同时以分析化学为基础,以微机电加工技术为依托,以微管道网络为结构特征,以生命科学为目前主要应用对象，是当前微全分析系统领域发展的重点。它的目标是把整个化验室的功能,包括采样、稀释、加试剂、反应、分离、检测等集成在微芯片上,且可以多次使用。微流控芯片具有液体流动可控、消耗试样和试剂极少、分析速度成十倍上百倍地提高等特点,它可以在几分钟甚至更短的时间内进行上百个样品的同时分析,并且可以在线实现样品的预处理及分析全过程。
目前限制微流控芯片大规模应用的一个重要原因是由于加工工艺的限制，不同芯片之间的差异会导致检测过程中系统误差增大。中国专利
CN1323393和美国专利6986837、
6498497、US20030011382揭示了一种完成筛选化验的微流体控制器和检测器系统和方法。微流体控制器和检测器系统包括流体芯片，芯片包括至少两个相交通道和检测区，流体导向系统包括与至少两个相交通道电接触的电学接口、具有放置在检测区附近的物镜的光学模块和与光学模块耦合并且适于接收和分析光学模块数据的控制系统。电学接口一般包括与相交通道电接触并且与电极通道耦合的电极，用于向电极提供电气输入。基准通道可以校正电极通道。但是该方法操作复杂，不利于微流芯片的实际应用。
本发明要解决的技术问题在于，针对现有技术的上述操作复杂，不利于实际应用的缺陷，提供一种操作简便、利于实际应用的对基于微流控芯片的检测系统进行自校准的方法及系统。
本发明解决其技术问题所采用的技术方案是：构造一种对基于微流控芯片的检测系统进行自校准的方法，其特征在于，包括以下步骤：
S1 ，将已知特性的基准微珠与分析样品混匀后，一同进入微流控芯片的检测区；
或者，
S1' ，将已知特性的基准微珠与分析样品隔开，所述基准微珠和分析样品分别通过微流控芯片的检测区；
S2
，所述检测区的检测通道每次仅允许一个所述基准微珠或分析样品的粒子通过，所述检测区的传感器检测所述基准微珠或分析样品产生的信号；
S3 ，将所述基准微珠的已知特性与检测结果进行比较，确定校准系数，校准所述
微流控芯片的检测区以及分析样品的检测结果。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，步骤S1中通过所述检测区时，所述基准微珠产生的信号与所述分析样品产生的信号具有显著差异；步骤S1'中所述
基准微珠与分析样品以空气隔开或以液体隔开，所述基准微珠内置在微流系统内。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述
检测区的传感器包括电学传感器、光学传感器。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述光学传感器至少检测前向散射、侧向散射、荧光信号中的一项。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述电学传感器至少检测电容和直流阻抗、射频阻抗、低频阻抗信号中的一项。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述基准微珠至少包括一种具有已知体积形状、或者具有已知光学特性或电学特性的颗粒。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述基准微珠的大小固定，且微珠最宽部分长度范围是10 nm - 1000
um，所述特征基准微珠的形状为球形、方形或三角形。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述基准微珠为实心、空心或含有特定荧光物质的颗粒。
在本发明所述的对微流控芯片的检测系统进行自校准的方法中，所述基准微珠的制作材料为玻璃、乳胶、硅胶、琼脂、树脂、塑料、陶瓷或金属。
还提供一种对基于微流控芯片的检测系统进行自校准的系统，包括基准微珠和微流控芯片，
所述基准微珠至少包括一种具有已知大小形状的、或者具有已知光学特性或电学特性的颗粒，所述基准微珠与所述分析样品混匀后通过所述微流控芯片的检测区，且通过所述检测区时，所述基准微珠产生的电学信号或光学信号与所述分析样品产生的电学信号或光学信号具有显著差异；或者所述基准微珠内置于微流控系统内与所述分析样品隔开，分别通过所述微流控芯片的检测区，
所述微流控芯片的检测通道每次仅允许一个所述基准微珠或分析样品的粒子通过，所述微流控芯片的传感器包括电学传感器、光学传感器，分别检测所述特征基准微珠和分析样品的光学特征或电学特征，并将检测结果与所述基准微珠已知的光学特性或电学特性进行比较，确定校准系数，对所述基于微流控芯片的检测系统进行自校准，从而校准所述分析样品的检测结果。
实施本发明提供的对基于微流控芯片的检测系统进行自校准的方法及系统，具有以下有益效果：操作简便，利于实际应用，能够使微流控芯片对分析样品的检测更为准确。
下面将结合附图及实施例对本发明作进一步说明，附图中：
图1是本发明对基于微流控芯片的检测系统进行自校准的方法第一实施例的自校准过程示意图；
图2是本发明对基于微流控芯片的检测系统进行自校准的方法第一实施例的自校准结果示意图；
图3是本发明对基于微流控芯片的检测系统进行自校准的方法第二实施例的自校准过程示意图；
图4是本发明对基于微流控芯片的检测系统进行自校准的方法第二实施例的自校准结果示意图；
图5是本发明对基于微流控芯片的检测系统进行自校准的方法第三实施例的自校准结果示意图。
为了对本发明的技术特征、目的和效果有更加清楚的理解，现对照附图详细说明本发明的具体实施方式。
微流分析产品指的是用于检测分析生物或化学样品的分析装置，其通过微蚀刻等技术在芯片上形成微米级的微通道，以供给或混合多种样品溶液和试剂，从而使液体能够在通道内进行反应，并在检测区进行信号检测。按照检测对象分类，一般可以分为DNA芯片、RNA芯片、蛋白质芯片及细胞芯片。其中,细胞芯片常用来分析酵母细胞、精子细胞、血细胞及肿瘤细胞等。
本发明提供了一种对基于微流控芯片的检测系统自校准的方法，所述方法包括在微流的溶液中加入固定大小、形状或颗粒性质的基准微珠，基准微珠通过检测区时产生的光学信号或电学信号可以对检测孔的大小进行自动校准，从而对分析样品的检测信号进行自动校正。本发明提供的方法可以对微流分析产品进行自校准，尤其是一次性微流产品，可以有效避免因制作工艺产生的检测区大小不一致而对检测信号的不利影响，增加了批量产品之间的一致性，有利于微流产品的大规模实际应用。
实施例1：自校准方法用于酵母测量微流控芯片
本实施例以细胞芯片为例，详细说明对基于微流控芯片的检测系统自校准的方法。
请参阅图1，为本发明对基于微流控芯片的检测系统进行自校准的方法第一实施例的自校准过程示意图。如图1所示，将10 um
的乳胶基准微珠内置在微流系统检测区之前，两端通过空气隔离。测试时，乳胶基准微珠首先通过检测区。检测区如图1所示，设置两个检测电极，对通过的乳胶基准微珠进行阻抗测量。箭头所示方向为乳胶基准微珠的流向。随后加入酵母细胞溶液，利用类似的方法进行信号检测。采用同样的样品分别用两个微流芯片进行检测，并分别选取100个酵母细胞和基准微珠的信号取平均值。
请参阅图2，为本发明对基于微流控芯片的检测系统进行自校准的方法第一实施例的自校准结果示意图。如图2所示，a是未经自校准的芯片1检测乳胶基准微珠的电压；b是未经自校准的芯片1检测酵母细胞的电压；c是未经自校准的芯片2检测乳胶基准微珠的电压；d是未经自校准的芯片2检测酵母细胞的电压；e是经过自校准的芯片1检测酵母细胞的电压；f是经过自校准的芯片2检测酵母细胞的电压。上述乳胶基准微珠均为同一种类，酵母细胞也均为同一种类。
两个微流芯片对酵母细胞的测量信号差别较大，但是经过同样的乳胶基准微珠进行信号校正之后，酵母细胞的测量结果基本一致，说明本发明提供的微流分析产品自校准的方法能够有效降低因制作工艺产生的检测区大小不一致而对检测信号的不利影响，增加了批量产品之间的一致性。同时该方法操作方便，不需要增加微流产品设计的复杂性，有利于微流产品的大规模实际应用。
实施例2：自校准方法用于精子分析微流控芯片
精子的数量和运动能力是评估男性生育能力的重要指标。请参阅图3，为本发明对微流控芯片的检测区进行自校准的方法第二实施例的自校准过程示意图。如图3所示，精子分析微流控芯片在检测通道内设置有检测孔，内置有1对电极传感器，由于精子本身的导电性较低，精子通过检测孔时，会使检测孔处液体的低频导电率下降，检测孔内的1对电极以电压脉冲的形式检测并记录这一阻抗变化。此原理即为库尔特原理，据此可以对一定时间和一定区域内的精子进行计数，进而换算出精子的数量和运动能力参数。
精子样品和5
um大小的基准微珠混合，一起加入到微流控分析芯片入口，精子和基准微珠一起通过微流道，进入检测孔。利用库尔特原理对颗粒进行计数的原理，精子和基准微珠单个通过检测孔时，会产生各自的阻抗信号，选取峰的面积进行阻抗数据分析，由于精子和基准微珠在大小和形状上有差异，因此，产生的阻抗信号各不相同，容易区分开。基准微珠通过检测区理论上应产生的平均阻抗信号为V，测量平均阻抗信号为Vm，基准微珠理论数量为N，测量基准微珠总量为Nc。精子测量的平均阻抗信号为Vs，精子的测量总数为Ns，则经过校正，精子的校正阻抗信号为Vs×Vm/V,精子的校正数量为Ns×Nc/N。
请参阅图4，为本发明对基于微流控芯片的检测系统进行自校准的方法第二实施例的自校准结果示意图。如图4所示，g是基准微珠的信号曲线；h是精子的信号曲线。由图4可以明显看出精子和基准微珠产生的阻抗信号各不相同，容易区分开，因此可以将二者混匀后一起经过检测区，通过基准微珠的信号对检测系统进行校正。
实施例3 自校准方法用于血细胞分析微流控芯片
血细胞计数属于医学领域中最为常见的血液检验项目之一，计数结果的异常增高或降低可能表示存在许多种疾病，可以提供关于病人总体健康状况的概览。血细胞计数的基本流程是，首先血液被等渗稀释液稀释，让悬浮在稀释液中的细胞排成单列顺序通过一个流通检测器，这时，细胞处于一束狭窄的聚焦光路中，每个血细胞穿过时，就会阻断一次光束，一定数量的细胞不断地打断光束，使检测器检出单位时间内光线阻断的次数，从而计算出细胞的数量。光散射法还可依据每个细胞通过时所产生的散射角度来判断每个细胞的体积和形态等特征。散射产生的前向散射光（FSC）、侧向散射光（SSC）可分别用于探测细胞体积大小和细胞内含物的情况（细胞核以及颗粒情况）。
血液样品稀释后和5
um大小的基准微珠混合，一起加入到微流控分析芯片入口，红细胞和基准微珠一起通过微流道，进入检测孔。细胞处于一束狭窄的聚焦光路中，通过检测器检出单位时间内光线阻断的次数，从而计算出细胞的数量，通过前向和侧向的光学传感器检测单个细胞通过产生的前向散射光（FSC）和侧向散射光（SSC）。校准基准微珠通过检测孔时，同样会阻断光束产生前向散射光（FSC）和侧向散射光（SSC）信号。由于红细胞和基准微珠在大小和内部颗粒结果上存在差异，因此，产生的前向散射光（FSC）和侧向散射光（SSC）信号各不相同，容易区分开。基准微珠通过检测区理论上应产生的平均前向散射光（FSC）信号为F，测量平均前向散射光信号为Fm，基准微珠通过检测区理论上应产生的平均侧向散射光信号为S，测量平均侧向散射光信号为Sm，基准微珠理论数量为N，测量基准微珠总量为Nc。红细胞测量的平均前向散射光信号为Fr，红细胞测量的平均侧向散射光信号为Sr，红细胞的测量总数为Nr，则经过校正，红细胞的校正前向散射光信号为Fr×Fm/F,
红细胞的校正侧向散射光信号为Sr×Sm/S，红细胞的校正数量为Nr×Nc/N。
请参阅图5，为本发明对基于微流控芯片的检测系统进行自校准的方法第三实施例的自校准结果示意图。如图5所示，i显示的是红细胞的散射信息；j显示的是基准微珠的散射信息。由图5可以明显看出红细胞和基准微珠产生的散射信号各不相同，容易区分开，因此也可以将二者混匀后一起经过检测区，通过基准微珠的信号对检测系统进行校正。
以上各实施例中的电极设计方式，为众多电极设计方式之一，本发明并不仅限于此。
用于微流分析的微流芯片的制作方法不做具体限定，例如可以可用PDMS结合玻片或硅片的方法，也可以采用热压成型法制备塑料微流控芯片（PMMA）。而且，对微流道的形状不做具体限定，例如进样口和检测区之间的微流道可以是直线、圆形、椭圆形及多边形等。
作为校准试剂的基准微珠，优选为球形，形态均匀，信号比较均一，基准微珠的材质优选为硅胶，制作比较方便。
上面结合附图对本发明的实施例进行了描述，但是本发明并不局限于上述的具体实施方式，上述的具体实施方式仅仅是示意性的，而不是限制性的，本领域的普通技术人员在本发明的启示下，在不脱离本发明宗旨和权利要求所保护的范围情况下，还可做出很多形式，这些均属于本发明的保护之内。
Claims (10)
- 一种对基于微流控芯片的检测系统进行自校准的方法，其特征在于，包括以下步骤：S1 ，将已知特性的基准微珠与分析样品混匀后，一同进入微流控芯片的检测区；或者，S1' ，将已知特性的基准微珠与分析样品隔开，所述基准微珠和分析样品分别通过 微流控芯片的检测区 ；S2 ，所述检测区的检测通道每次仅允许一个所述基准微珠或分析样品的粒子通过，所述检测区的传感器检测所述基准微珠或分析样品产生的信号；S3 ，将所述基准微珠的已知特性与检测结果进行比较，确定校准系数，校准所述 微流控芯片的检测区以及分析样品的检测结果。
- 根据权利要求1所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，步骤S1中通过所述检测区时，所述基准微珠产生的信号与所述分析样品产生的信号具有显著差异；步骤S1’中所述基准微珠与分析样品以空气隔开或以液体隔开，所述基准微珠内置在微流系统内。
- 根据权利要求1所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述检测区的传感器包括电学传感器、光学传感器。
- 根据权利要求3所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述光学传感器至少检测前向散射、侧向散射、荧光信号中的一项。
- 根据权利要求3所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述电学传感器至少检测电容和直流阻抗、射频阻抗、低频阻抗信号中的一项。
- 根据权利要求1所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述基准微珠至少包括一种具有已知体积形状、或者具有已知光学特性或电学特性的颗粒。
- 根据权利要求6所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述基准微珠的大小固定，且微珠最宽部分长度范围是10 nm - 1000 um，所述特征基准微珠的形状为球形、方形或三角形。
- 根据权利要求6所述的对基于微流控芯片的检测系统进行自校准的方法，其特征在于，所述基准微珠为实心、空心或含有特定荧光物质的颗粒。
- 根据权利要求6所述的对微流控芯片的检测系统进行自校准的方法，其特征在于，所述基准微珠的制作材料为玻璃、乳胶、硅胶、琼脂、树脂、塑料、陶瓷或金属。
- 一种对基于微流控芯片的检测系统进行自校准的系统，其特征在于，包括基准微珠和微流控芯片，所述基准微珠至少包括一种具有已知大小形状的、或者具有已知光学特性或电学特性的颗粒，所述基准微珠与所述分析样品混匀后通过所述微流控芯片的检测区，且通过所述检测区时，所述基准微珠产生的电学信号或光学信号与所述分析样品产生的电学信号或光学信号具有显著差异；或者所述基准微珠内置于微流控系统内与所述分析样品隔开，分别通过所述微流控芯片的检测区，所述微流控芯片的检测通道每次仅允许一个所述基准微珠或分析样品的粒子通过，所述微流控芯片的传感器包括电学传感器、光学传感器，分别检测所述特征基准微珠和分析样品的光学特征或电学特征，并将检测结果与所述基准微珠已知的光学特性或电学特性进行比较，确定校准系数，对所述基于微流控芯片的检测系统进行自校准，从而校准所述分析样品的检测结果。
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