CN110208351B - Method and device for detecting hematocrit - Google Patents
Method and device for detecting hematocrit Download PDFInfo
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- CN110208351B CN110208351B CN201910551123.7A CN201910551123A CN110208351B CN 110208351 B CN110208351 B CN 110208351B CN 201910551123 A CN201910551123 A CN 201910551123A CN 110208351 B CN110208351 B CN 110208351B
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Abstract
The embodiment of the application provides a method for detecting hematocrit, which comprises the steps of obtaining an impedance difference value delta I between an IWB and an IRB according to an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on a sensor test strip and an impedance value IRB of a loop formed by the reference electrode, the blank electrode and the sample to be detected; obtaining a functional relation between the hematocrit and the impedance difference value delta I according to the impedance difference value delta I and the experimental data of the hematocrit; the hematocrit measurement is performed as a function of the hematocrit and the impedance difference Δ I. The embodiment of the application can reduce the negative influence on the hematocrit detection caused by the inconsistent thickness degree of the carbon electrode on the sensor test strip, improve the accuracy of the hematocrit detection and further improve the accuracy of the physiological diagnosis result obtained by detecting the hematocrit as a correction means.
Description
Technical Field
The embodiment of the application relates to the technical field of data processing, in particular to a method and a device for detecting hematocrit.
Background
An electrochemical biosensor test strip for in vitro physiological diagnosis generally comprises three electrodes, namely a working electrode, a reference electrode and a blank electrode. In the process of detecting physiological signals, after a sample to be detected enters a sensor strip, a working electrode and a blank electrode of the sensor strip are matched with each other to obtain an initial signal of the sample to be detected, a reference electrode and the blank electrode are matched with each other to obtain a background signal of the sample to be detected, and the initial signal is subtracted from the background signal to obtain relatively accurate physiological signals.
In the prior art, in order to further improve the accuracy of detecting physiological signals, the Hematocrit (HCT) of the sample to be detected is generally obtained to correct the detection result. The conventional method for detecting HCT includes obtaining multiple sets of HCT values and impedance value data of the sensor strip through experiments, performing curve fitting on the multiple sets of data to obtain an HCT function, and then substituting the impedance value of a loop formed by the sensor strip and a sample to be detected into the HCT function to obtain the HCT value of the sample to be detected.
However, in practice, carbon is generally used as a material for making the electrode in order to achieve both the conductivity of the electrode and the production cost, and in the process of printing the electrode, due to the limitation of the printing process, the thickness of the carbon electrode inevitably varies, so that the impedance of the carbon electrode varies from one sensor strip to another, therefore, the impedance values of the loops formed by different sensor test strips and the sample to be detected have deviation, and the impedance value data of the sensor test strips obtained through experiments contains the impedance values of the electrodes of the sensor test strips, therefore, the HCT value of the sample to be detected obtained by substituting the impedance value of the loop formed by the sensor test strip and the sample to be detected into the HCT function and the actual HCT value of the sample to be detected have deviation, and the accuracy of the physiological diagnosis result obtained by HCT correction is further reduced.
Disclosure of Invention
In view of this, one of the technical problems solved by the embodiments of the present application is to provide a method for detecting hematocrit, which is used for detecting hematocrit by establishing a functional relationship between the hematocrit and an impedance of a sample to be detected, so as to reduce negative effects on HCT detection caused by inconsistent thickness of carbon electrodes on a sensor strip, improve accuracy of HCT detection, and further improve accuracy of a physiological diagnosis result obtained by detecting HCT as a correction means.
In a first aspect, an embodiment of the present application provides a method for detecting hematocrit, where the method obtains an impedance difference Δ I between an IWB and an IRB according to an impedance value IWB of a loop formed by a working electrode, a blank electrode, and a sample to be detected on a sensor strip and an impedance value IRB of a loop formed by a reference electrode, a blank electrode, and a sample to be detected; obtaining a functional relation between the hematocrit and the impedance difference value delta I according to the impedance difference value delta I and the experimental data of the hematocrit; the hematocrit measurement is performed as a function of the hematocrit and the impedance difference Δ I.
Optionally, the impedance difference Δ I is an absolute value | IWB-IRB | of a difference between IWB and IRB.
Optionally, the reference electrode has a length equal to or greater than the working electrode.
In a second aspect, an embodiment of the present application further provides an apparatus for detecting hematocrit, which includes an electrode detection module, an impedance difference module, a functional relation module, and a detection module, wherein:
the electrode detection module is connected with the impedance difference module and is used for detecting an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on the sensor test strip and an impedance value IRB of a loop formed by a reference electrode, the blank electrode and the sample to be detected and sending the detected IWB and IRB to the impedance difference module;
the impedance difference module is connected with the electrode detection module and the functional relation module and is used for obtaining an impedance difference value delta I of the IWB and the IRB according to the IWB and the IRB obtained from the electrode detection module and sending the obtained impedance difference value delta I to the functional relation module;
the functional relation module is connected with the impedance difference module and the detection module, and is used for obtaining the functional relation between the hematocrit and the impedance difference value delta I according to the impedance difference value delta I and the experimental data of the hematocrit obtained from the impedance difference module and sending the obtained functional relation to the detection module;
the detection module is connected with the functional relation module and is used for detecting the hematocrit according to the relationship between the hematocrit and the impedance difference value delta I obtained from the functional relation module.
In a third aspect, the present application further provides a storage medium including a stored program, where the program is executed to perform the method for detecting hematocrit.
In a fourth aspect, an embodiment of the present application further provides an electronic device, which includes a memory, a processor, and a computer program stored in the memory and executable on the processor, where the processor executes the method for detecting hematocrit.
It can be seen from the above technical solutions that, in the embodiment of the present application, according to the impedance value IWB of the loop formed by the working electrode, the blank electrode and the sample to be detected on the sensor strip and the impedance value IRB of the loop formed by the reference electrode, the blank electrode and the sample to be detected, the impedance difference Δ I between IWB and IRB is obtained, and the functional relationship between the hematocrit and the impedance difference Δ I is obtained through multiple pairs of impedance difference Δ I and the experimental data of the hematocrit obtained through multiple experiments, compared with the functional relationship between the hematocrit and IWB or IRB obtained through the experimental data of multiple pairs of IWB or IRB and hematocrit in the prior art, the linear relationship between the function of the hematocrit and the impedance difference Δ I and the impedance of the sample to be detected is strongest, so that the hematocrit function obtained in the embodiment of the present application is prestored in the in-vitro physiological diagnostic apparatus, the detected hematocrit value is more accurate than the hematocrit value obtained by the prior art.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments described in the embodiments of the present application, and other drawings can be obtained by those skilled in the art according to the drawings.
FIG. 1 is a schematic diagram of a carbon electrode on a sensor strip in an embodiment of the present application;
FIG. 2 is a schematic flow chart illustrating a method for detecting hematocrit in an embodiment of the present application;
FIG. 3A is a diagram illustrating HCT functions obtained from experimental data of HCT and IWB in the prior art;
FIG. 3B is a schematic diagram of HCT function obtained from experimental data of HCT and IRB in the prior art;
FIG. 3C is a schematic diagram of an HCT function obtained according to experimental data of HCT and an impedance difference Δ I in the prior art;
FIG. 4 is a schematic diagram of an apparatus for detecting hematocrit in an embodiment of the present application;
fig. 5 is a schematic structural diagram of a storage medium in an embodiment of the present application.
Detailed Description
In order to make those skilled in the art better understand the technical solutions in the embodiments of the present application, the technical solutions in the embodiments of the present application will be described clearly and completely below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, but not all embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments in the present application shall fall within the scope of the protection of the embodiments in the present application.
The structure of the sensor test strip is shown in fig. 1, a blank electrode B, a reference electrode R and a working electrode W are arranged on the sensor test strip in sequence along a sample introduction end, an electric contact end of the sensor test strip is connected with a sensor, a sample to be detected enters a sample cavity of the sensor test strip from the sample introduction end of the sensor test strip, and the sensor can complete the detection of physiological signals. In the prior art, an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample on a sensor test strip is generally detected, and the IWB is substituted into an HCT function to calculate an HCT value; or detecting the impedance value IRB of a loop formed by the reference electrode, the blank electrode and the sample on the sensor test strip, and substituting the IRB into the HCT function to calculate the HCT value. However, whether detecting IWB or detecting IRB, the impedance values of the loops formed by different sensor strips and the detection sample all include the impedance of the electrode itself on the sensor strip, and the impedance of the electrode itself is different due to the different thickness of the electrode, so the accuracy of the detected HCT value is reduced.
Based on the problem of low accuracy of the HCT value detected in the prior art, as shown in fig. 2, the embodiment of the present application provides a method for detecting hematocrit, which includes steps S100 to S300, specifically:
s100: and obtaining an impedance difference value delta I of the IWB and the IRB according to an impedance value IWB of a loop formed by the working electrode, the blank electrode and the sample to be detected on the sensor test strip and an impedance value IRB of a loop formed by the reference electrode, the blank electrode and the sample to be detected.
For the sensor test strip, the sum of the impedance IW of the working electrode, the impedance IB of the blank electrode and the impedance IS1 of the sample to be detected between the working electrode and the blank electrode, that IS, IW + IB + IS1 IS the impedance IWB of a loop formed by the working electrode, the blank electrode and the sample to be detected on the sensor test strip; similarly, the impedance IR of the reference electrode itself, the impedance IB of the blank electrode itself, and the impedance IS2 of the sample to be detected between the reference electrode and the blank electrode, i.e. IR + IB + IS2 are the impedance values IRB of the circuit formed by the reference electrode, the blank electrode and the sample to be detected.
After obtaining IWB and IRB, the impedance difference Δ I between IWB and IRB can be obtained. Δ I ═ IW + IB + IS1) - (IR + IB + IS2 ═ IW-IR) + (IS1-IS2), i.e. the impedance difference Δ I IS the impedance difference between the sample to be detected and the working electrode IW and the reference electrode IR.
Alternatively, the length of the reference electrode is equal to or greater than the working electrode, and as can be seen from FIG. 1, the length of the reference electrode is greater than the working electrode, and theoretically the impedance IR of the reference electrode is greater than the impedance IW of the working electrode. On one hand, however, the size of the sensor strip itself is very small, and generally the length of a single sensor strip is about 3 cm, and the difference between the lengths of the working electrode and the reference electrode is about within 3 mm, i.e. the difference between the lengths of the working electrode and the reference electrode is negligible relative to the length of the single sensor strip itself; on the other hand, because the carbon electrode has better conductivity, the impedance itself is relatively small, and in addition, the thicknesses of the working electrode and the reference electrode on the same sensor strip are basically the same, so the impedance IW of the working electrode and the impedance IR of the reference electrode can be considered to be approximately the same, that is, IW and IR can be considered to be the same. As can be further seen from fig. 1, the sample area between the reference electrode and the blank electrode IS smaller than that between the working electrode and the blank electrode, so that IS1 IS larger than that of IS2, and then according to the formula of the impedance difference Δ I between IWB and IRB, (IW + IB + IS1) - (IR + IB + IS2) — (IW-IR) + (IS1-IS2), the impedance difference Δ I can be regarded as the sample impedance difference to be detected between the two groups of electrodes, i.e., the impedance difference Δ I IS1-IS 2.
In practical operation, the arrangement order of the electrodes may be different from that in fig. 1, so that the sample area between the reference electrode and the blank electrode IS not necessarily smaller than that between the working electrode and the blank electrode, i.e., IS1 IS not necessarily larger than IS2, and therefore, in the embodiment of the present application, the impedance difference Δ I IS the absolute value of the difference between IWB and IRB, i.e., the impedance difference Δ I ═ IWB-IRB |.
Since the impedance of the sample to be detected is in a functional relationship with the HCT of the sample to be detected, the impedance difference Δ I is also in a functional relationship with the HCT of the sample to be detected. After obtaining the impedance difference Δ I, step S200 is executed: and obtaining a functional relation between the hematocrit and the impedance difference value delta I according to the impedance difference value delta I and the experimental data of the hematocrit.
Specifically, in the embodiment of the present application, a curve fitting is performed according to the data of the impedance difference Δ I and the HCT, so as to obtain a functional relationship between the HCT and the impedance difference Δ I.
In practical operation, a plurality of pairs of experimental data of the impedance difference values Δ I and HCT can be obtained through a plurality of experiments, and the impedance difference values Δ I and HCT are in one-to-one correspondence in each group of data.
After obtaining the functional relationship between HCT and the impedance difference Δ I, step S300 may be executed, specifically:
s300: the hematocrit measurement is performed as a function of the hematocrit and the impedance difference Δ I.
And in actual test, the sensor firstly detects IWB and IRB of the sensor test strip, then calculates the impedance difference value delta I of the IWB and the IRB, and substitutes the impedance difference value delta I into the pre-stored HCT function to calculate the more accurate HCT value of the sample to be detected.
Compared with the prior art, a plurality of groups of HCT values and impedance value data of the sensor test strip are obtained through experiments, wherein the impedance value data of the sensor test strip comprise impedance values of electrodes on the sensor test strip, and an HCT function obtained by curve fitting the plurality of groups of data is obtained.
In the embodiment of the application, in order to verify the effect of detecting the HCT value by the HCT function obtained by curve fitting of the impedance difference value delta I and the HCT, 7 samples to be detected with different HCTs are selected, sensor test strips of the same batch are selected, the samples with each HCT value are tested, in addition, in order to reduce human errors in the testing process, the samples with each HCT value are tested for 6 times, IWB and IRB of each test are recorded, and then the average impedance difference value of 6 times is calculated to serve as the impedance difference value delta I.
An HCT function obtained by curve fitting IWB and HCT according to the prior art is shown in FIG. 3A, and an HCT function obtained by curve fitting IRB and HCT according to the prior art is shown in FIG. 3B. The HCT function obtained by curve fitting the average impedance difference Δ I and HCT of 6 times in the above example is shown in fig. 3C, and the obtained HCT function is shown in table 2.
The HCT value obtained by substituting the IWB of each sample into the HCT function in FIG. 3A is recorded as HCT1, and the deviation from the actual HCT value is recorded as BIAS 1; the HCT value obtained by substituting the IRB of each sample into the HCT function shown in FIG. 3B is recorded as HCT2, and the deviation of the HCT value from the actual HCT value is recorded as BIAS 2; the HCT value obtained by substituting the impedance difference Δ I for each sample into the HCT function of fig. 3C is HCT3, and its deviation from the actual HCT value is denoted BIAS 3. Note that the deviations BIAS1, BIAS2, and BIAS3 are absolute values of the differences between the actual HCT value and the HCT value calculated by the functions shown in fig. 3A, 3B, and 3C. The actual HCT values, the specific data for each IWB, IRB and Δ I, HCT1, HCT2, HCT3, BIAS1, BIAS2 and BIAS3 for each sample tested are shown in table 1 below:
TABLE 17 test results of 6 tests of each sample to be tested
TABLE 2 fitting function Table of IWB, IRB and Δ I and HCT
| No | Curve fitting object | Curve fitting function | Correlation coefficient |
| 1 | IWB&HCT | Y＝1.8471X-12.923 | 0.9876 |
| 2 | IRB&HCT | Y＝2.7682X-18.367 | 0.9716 |
| 3 | ΔI&HCT | Y＝5.4263X-1.061 | 0.9967 |
As can be seen from the data in table 1, BIAS3 is mostly smaller than BIAS1 and BIAS2, and even though BIAS3 is larger than BIAS1 and BIAS2, it is very close to BIAS1 and BIAS 2. In some cases, BIAS3 is much smaller than BIAS1 and BIAS 2. The data in table 1 fully illustrate that using the impedance difference Δ I as a parameter in the HCT function improves the accuracy of the calculated HCT value.
As can be seen from table 2, the correlation coefficient of the HCT function obtained by fitting the impedance difference Δ I and the HCT curve is the largest.
Compared with the prior art, the method for detecting HCT in the embodiment of the application carries out curve fitting by using the impedance difference value between the IWB and the IRB and HCT and carries out HCT detection as a function of HCT, so that the influence of the manufacturing process on the impedance of the electrode on the sensor test strip can be eliminated, and the HCT detection accuracy is improved.
Based on the same inventive concept, as shown in fig. 4, an embodiment of the present application further provides an apparatus for detecting hematocrit, which includes an electrode detection module 401, an impedance difference module 402, a functional relationship module 403, and a detection module 404, wherein:
the electrode detection module 401 is connected with the impedance difference module 402, and is configured to detect an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on the sensor strip and an impedance value IRB of a loop formed by a reference electrode, a blank electrode and a sample to be detected, and send the detected IWB and IRB to the impedance difference module 402;
the impedance difference module 402 is connected to the electrode detection module 401 and the functional relation module 403, and configured to obtain an impedance difference Δ I between the IWB and the IRB according to the IWB and the IRB obtained from the electrode detection module 401, and send the obtained impedance difference Δ I to the functional relation module 403;
the functional relationship module 403 is connected to the impedance difference module 402 and the detection module 404, and configured to obtain a functional relationship between the hematocrit and the impedance difference Δ I according to the impedance difference Δ I and the hematocrit test data obtained from the impedance difference module 402, and send the obtained functional relationship to the detection module 404;
the detecting module 404 is connected to the functional relation module 403, and is configured to perform hematocrit detection according to the relationship between the hematocrit and the impedance difference Δ I obtained from the functional relation module 403.
The electrode detection module 401, the impedance difference module 402, the functional relationship module 403 and the detection module 404 are used to perform the method for detecting hematocrit according to the above-described embodiments.
The embodiment of the application also provides a storage medium comprising a stored program, wherein the program is executed to execute the method for detecting the hematocrit in the embodiment.
The embodiment of the present application further provides an electronic device, as shown in fig. 5, the electronic device 50 includes a memory 502, a processor 501 and a computer program stored on the memory 502 and executable on the processor 501, and the processor 501 executes the method for detecting hematocrit in the above embodiment through the computer program.
In an exemplary embodiment, when the processor 501 performs hematocrit detection according to a functional relationship between the hematocrit and the impedance difference Δ I, and obtains the functional relationship between the hematocrit and the impedance difference Δ I according to the experimental data of the impedance difference Δ I and the hematocrit, the impedance difference Δ I is an absolute value | IWB-IRB | of a difference between IWB and IRB.
In an exemplary embodiment, the processor 501 detects the length of the reference electrode on the sensor strip as equal to or greater than the working electrode.
The electronic device provided in the embodiment of the present application may be a terminal device, which may be a smart phone, a tablet computer, or the like, and the terminal device is configured to execute the method for detecting hematocrit described in the embodiments corresponding to fig. 1 to fig. 5.
The terminal device may include one or more of the following components: processing components, memory, power components, multimedia components, audio components, interfaces for input/output (I/O), sensor components, and communication components.
The processing component typically controls overall operation of the terminal device, such as operations associated with display, telephone calls, data communications, camera operations and recording operations. The processing components may include one or more processors to execute instructions to perform all or a portion of the steps of the methods described above. Further, the processing component can include one or more modules that facilitate interaction between the processing component and other components. For example, the processing component may include a multimedia module to facilitate interaction between the multimedia component and the processing component.
The memory is configured to store various types of data to support operations at the terminal device. Examples of such data include instructions for any application or method operating on the terminal device, contact data, phonebook data, messages, pictures, videos, etc. The Memory may be implemented by any type of volatile or non-volatile Memory device or combination thereof, such as Static Random Access Memory (SRAM), Electrically Erasable Programmable Read Only Memory (EPROM), Programmable Read Only Memory (PROM), Read Only Memory (ROM), magnetic Memory, flash Memory, magnetic disk or optical disk.
The power supply component provides power to various components of the terminal device. The power components may include a power management system, one or more power sources, and other components associated with generating, managing, and distributing power for the terminal device.
The multimedia component includes a screen providing an output interface between the terminal device and the user. In some embodiments, the screen may include a Liquid Crystal Display (LCD) and a Touch Panel (TP). If the screen includes a touch panel, the screen may be implemented as a touch screen to receive an input signal from a user. The touch panel includes one or more touch sensors to sense touch, slide, and gestures on the touch panel. The touch sensor may not only sense the boundary of a touch or slide action, but also detect the duration and pressure associated with the touch or slide operation. In some embodiments, the multimedia component includes a front facing camera and/or a rear facing camera. When the terminal device is in an operation mode, such as a shooting mode or a video mode, the front camera and/or the rear camera can receive external multimedia data. Each front camera and rear camera may be a fixed optical lens system or have a focal length and optical zoom capability.
The audio component is configured to output and/or input an audio signal. For example, the audio component may include a Microphone (MIC) configured to receive external audio signals when the terminal device is in an operating mode, such as a call mode, a recording mode, and a voice recognition mode. The received audio signal may further be stored in a memory or transmitted via a communication component. In some embodiments, the audio assembly further comprises a speaker for outputting audio signals.
The I/O interface provides an interface between the processing component and a peripheral interface module, which may be a keyboard, click wheel, button, etc. These buttons may include, but are not limited to: a home button, a volume button, a start button, and a lock button.
The sensor assembly includes one or more sensors for providing various aspects of status assessment for the terminal device. For example, the sensor assembly may detect an open/closed state of the terminal device, the relative positioning of the components, such as a display and keypad of the terminal device, the sensor assembly may also detect a change in position of the terminal device or a component of the terminal device, the presence or absence of user contact with the terminal device, orientation or acceleration/deceleration of the terminal device, and a change in temperature of the terminal device. The sensor assembly may include a proximity sensor configured to detect the presence of a nearby object in the absence of any physical contact. The sensor assembly may also include a photosensor, such as a Complementary Metal Oxide Semiconductor (CMOS) or Charge Coupled Device (CCD) image sensor, for use in imaging applications. In some embodiments, the sensor assembly may further include an acceleration sensor, a gyroscope sensor, a magnetic sensor, a pressure sensor, or a temperature sensor.
The communication component is configured to facilitate wired or wireless communication between the terminal device and other devices. The terminal device may access a Wireless network based on a communication standard, such as Wireless Fidelity (WiFi), 2G or 3G, or a combination thereof. In an exemplary embodiment, the communication component receives a broadcast signal or broadcast related information from an external broadcast management system via a broadcast channel. In an exemplary embodiment, the Communication component further comprises a Near Field Communication (NFC) module to facilitate short-range Communication. For example, the NFC module may be implemented based on Radio Frequency Identification (RFID) technology, Infrared Data Association (IrDA) technology, Ultra Wideband (UWB) technology, Bluetooth (BT) technology, and other technologies.
In an exemplary embodiment, the terminal Device may be implemented by one or more Application Specific Integrated Circuits (ASICs), Digital Signal Processors (DSPs), Digital Signal Processing Devices (DSPDs), Programmable Logic Devices (PLDs), Field Programmable Gate Arrays (FPGAs), controllers, microcontrollers, microprocessors or other electronic components for performing the method for detecting hematocrit described in the embodiments corresponding to fig. 1-5.
In an exemplary embodiment, a non-transitory computer-readable storage medium comprising instructions, such as a memory comprising instructions, executable by a processing component of a terminal device to perform the above-described method is also provided. For example, the non-transitory computer readable storage medium may be a ROM, a Random Access Memory (RAM), a CD-ROM, a magnetic tape, a floppy disk, an optical data storage device, and the like. When the instructions in the storage medium are executed by a processing component of the terminal device, the terminal device is enabled to execute the method for detecting hematocrit as described in the embodiments corresponding to fig. 1 to 5 above, and the method includes:
obtaining an impedance difference value delta I of IWB and IRB according to an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on a sensor test strip and an impedance value IRB of a loop formed by a reference electrode, the blank electrode and the sample to be detected;
obtaining a functional relation between the hematocrit and the impedance difference value delta I according to the impedance difference value delta I and the experimental data of the hematocrit;
the hematocrit measurement is performed as a function of the hematocrit and the impedance difference Δ I.
The terminal device and the storage medium provided by the embodiment of the application carry out the detection of the hematocrit by establishing the functional relation between the hematocrit and the impedance of the sample to be detected, can reduce the negative influence on HCT detection caused by the inconsistent thickness degree of the carbon electrode on the sensor test strip, improve the accuracy of HCT detection, and further improve the accuracy of the physiological diagnosis result obtained by detecting HCT as a correction means.
Other embodiments of the disclosure will be apparent to those skilled in the art from consideration of the specification and practice of the disclosure disclosed herein. This application is intended to cover any variations, uses, or adaptations of the disclosure following, in general, the principles of the disclosure and including such departures from the present disclosure as come within known or customary practice within the art to which the disclosure pertains. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the disclosure being indicated by the following claims.
It will be understood that the present disclosure is not limited to the precise arrangements described above and shown in the drawings and that various modifications and changes may be made without departing from the scope thereof. The scope of the present disclosure is limited only by the appended claims. In the above embodiments, the descriptions of the respective embodiments have respective emphasis, and reference may be made to the related descriptions of other embodiments for parts that are not described or illustrated in a certain embodiment.
Claims (10)
1. A method of detecting hematocrit, comprising:
obtaining an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on a sensor test strip and an impedance value IRB of a loop formed by a reference electrode, the blank electrode and the sample to be detected;
obtaining an impedance difference value delta I of the IWB and the IRB according to the IWB and the IRB;
and determining the hematocrit according to the corresponding relation between the prestored impedance difference value delta I and the hematocrit.
2. The method for detecting hematocrit of claim 1, wherein the obtaining of the correspondence between the impedance difference Δ I and the hematocrit includes:
determining an impedance difference value delta I of the experimental data of the IWB and the IRB according to the experimental data of the IWB and the IRB;
performing curve fitting according to the impedance difference value delta I and corresponding experimental data of the hematocrit;
and determining the corresponding relation between the impedance difference value delta I and the hematocrit according to the curve fitting result.
3. The method of claim 2, wherein the IWB test data, the IRB test data, and the hematocrit test data are all at least three.
4. A method of measuring hematocrit according to claim 2 or 3, wherein at least three hematocrit test data are different from each other.
5. The method of detecting hematocrit of claim 4, wherein prior to the curve fitting based on the impedance difference Δ I and the corresponding experimental data of hematocrit includes:
testing the sensor test strip corresponding to each erythrocyte specific ratio value at least three times to obtain IRB and IWB of each time;
the absolute value of the difference between the average of at least three IRBs and the average of at least three IWBs is taken as the impedance difference value Δ I.
6. The device for detecting the hematocrit is characterized by comprising a first impedance obtaining module, a second impedance obtaining module, an impedance difference value module and a hematocrit module, wherein:
the first impedance acquisition module is used for acquiring an impedance value IWB of a loop formed by a working electrode, a blank electrode and a sample to be detected on the sensor test strip;
the second impedance obtaining module is used for obtaining an impedance value IRB of a loop formed by the reference electrode, the blank electrode and the sample to be detected;
the impedance difference module is used for obtaining an impedance difference value delta I between the IWB and the IRB according to the IWB and the IRB;
the hematocrit module is used for determining the hematocrit according to the corresponding relation between the prestored impedance difference value delta I and the hematocrit.
7. The apparatus for detecting hematocrit of claim 6, further comprising a module for obtaining a correspondence between the impedance difference Δ I and the hematocrit, for:
determining an impedance difference value delta I of the experimental data of the IWB and the IRB according to the experimental data of the IWB and the IRB;
performing curve fitting according to the impedance difference value delta I and corresponding experimental data of the hematocrit;
and determining the corresponding relation between the impedance difference value delta I and the hematocrit according to the curve fitting result.
8. The apparatus according to claim 7, wherein the correspondence between the difference in impedance Δ I and the hematocrit is determined by the module for obtaining correspondence between the difference in impedance Δ I and the hematocrit in at least three of the experimental data of IWB, the experimental data of IRB, and the experimental data of hematocrit.
9. An apparatus for measuring hematocrit according to claim 7 or 8, wherein at least three of the hematocrit test data are different from each other.
10. The apparatus for detecting hematocrit of claim 9, wherein the module for obtaining a correspondence between the impedance difference Δ I and the hematocrit further includes, before determining the correspondence between the impedance difference Δ I and the hematocrit:
testing the sensor test strip corresponding to each erythrocyte specific ratio value at least three times to obtain IRB and IWB of each time;
the absolute value of the difference between the average of at least three IRBs and the average of at least three IWBs is taken as the impedance difference value Δ I.
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