CN114271809A - Manual calibration method and system for human body respiratory flow test - Google Patents
Manual calibration method and system for human body respiratory flow test Download PDFInfo
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- 230000000241 respiratory effect Effects 0.000 title claims abstract description 34
- 238000000034 method Methods 0.000 title claims abstract description 29
- 238000012360 testing method Methods 0.000 title claims abstract description 24
- 239000012530 fluid Substances 0.000 claims description 10
- 238000004088 simulation Methods 0.000 claims description 5
- 238000013500 data storage Methods 0.000 claims description 3
- 230000008569 process Effects 0.000 description 10
- 230000009325 pulmonary function Effects 0.000 description 6
- 230000029058 respiratory gaseous exchange Effects 0.000 description 3
- 238000004364 calculation method Methods 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000004199 lung function Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 208000019693 Lung disease Diseases 0.000 description 1
- 230000001186 cumulative effect Effects 0.000 description 1
- 238000009795 derivation Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000004134 energy conservation Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000013123 lung function test Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000003908 quality control method Methods 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
- 238000009423 ventilation Methods 0.000 description 1
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Abstract
The invention discloses a manual calibration method and a system for a human body respiratory flow test in the technical field of flow calibration, wherein the manual calibration method for the human body respiratory flow test comprises the following steps: step one, collecting differential pressure values corresponding to different respiratory flow rates; extracting a pressure difference value, and establishing a piecewise linear nonlinear relation between the pressure difference value and a flow coefficient under different flow velocities; and step three, calculating calibration coefficients under other flow rates according to the piecewise linearity in the nonlinear relation in the step two, and completing flow calibration.
Description
Technical Field
The invention relates to the technical field of flow calibration, in particular to a manual calibration method and system for a human body respiratory flow test.
Background
The detection of lung function has become one of three diagnoses of clinical lung diseases, so the application of lung function test instruments is becoming more and more extensive. When the pulmonary function tester is used for testing indexes such as Forced Vital Capacity (FVC), Vital Capacity (VC), maximum Minute Ventilation Volume (MVV) and the like, the pulmonary function tester is easily influenced by conditions such as a sensor, temperature, humidity and the like, and the pulmonary function diagnostic result of a patient can be influenced. In order to meet the quality control requirement of the pulmonary function tester, daily calibration and calibration of the index of the pulmonary function tester are necessary.
The error sources of the lung function calibration in the prior art include density changes caused by air temperature and humidity, and nonlinear errors of an airspeed head and a pressure sensor, wherein each test scene of a customer with the former error changes, and the latter nonlinear error is related to sensor hardware and is basically determined after leaving a factory.
However, in the process of implementing the technical solution of the invention in the embodiments of the present application, the inventors of the present application find that the above-mentioned technology has at least the following technical problems:
the instrument for calibrating the pulmonary function instrument is generally in a calibration barrel structure, calibration under each flow rate is realized by pulling and pulling the calibration barrel for many times, and a calibration result is inaccurate due to a fault in the process and needs to be calibrated again.
Based on the above, the invention designs a manual calibration method and system for human respiratory flow test, so as to solve the above problems.
Disclosure of Invention
The invention provides a manual calibration method and system for a human body respiratory flow test, and aims to solve the technical problems that the manual calibration of the existing differential pressure sensor needs to be carried out for multiple times under different speeds to carry out normal measurement, and the manual calibration is relatively time-consuming and complicated to finish under the conditions of high speed and low speed.
In order to achieve the purpose, the invention adopts the following technical scheme:
a manual calibration method for a human body respiratory flow test comprises the following steps:
step one, collecting differential pressure values corresponding to different respiratory flow rates;
extracting a pressure difference value, and establishing a piecewise linear nonlinear relation between the pressure difference value and a flow coefficient under different flow velocities;
and step three, calculating calibration coefficients under other flow velocities according to the piecewise linearity in the nonlinear relation in the step two, and completing flow calibration.
Preferably, the respiratory flow rate in the first step is a flow rate under a simulated respiratory flow.
Preferably, the flow rate is the volume of fluid passing through the flow cross section per unit time.
Preferably, the flow rate includes flow rate intervals arranged from small to large.
Preferably, the establishing of the nonlinear relationship in the second step includes:
and respectively calculating the proportional relation between the coefficient in each flow velocity interval and the coefficients in other different flow velocity intervals according to the measured pressure difference value and the standard flow velocity.
Preferably, the flow rate interval at least comprises a low speed, a medium-low speed, a medium-high speed and a high speed.
Preferably, the acquiring of the other flow rates comprises:
and collecting the fluid volume calibration data pushed and pulled once by the standard 3L calibration cylinder, and transmitting the data to the system.
A manual calibration system for human body respiratory flow test comprises:
the breath flow rate simulation module is used for simulating differential pressure values of different breath flows at corresponding flow rates;
the data storage module is used for establishing and storing a nonlinear relation of piecewise linearity between flow coefficients under different flow velocities; and
and the flow calibration module is used for acquiring volume calibration data and acquiring a calibration coefficient under nonlinear relation piecewise linearity.
One or more technical solutions provided in the embodiments of the present invention have at least the following technical effects or advantages:
1. the invention deeply distinguishes the system error sources by adopting the matching control of different factory and user calibration methods, and coordinates with a high-precision simulation device of a manufacturer to calibrate the nonlinear error relation fixed by the system, and then calibrates the air density error by a simple volume calibration device of a client, thereby not only ensuring the accuracy of the system, but also simplifying the use calibration process of the user;
2. according to the invention, the nonlinear coefficient relation is calibrated in sections when leaving the factory, so that the actual calibration process of a user is simplified, and the calibration precision is improved;
in conclusion, the invention has the advantages of simple and convenient flow calibration, accurate calibration result and the like.
Drawings
The invention is described in further detail below with reference to the following figures and detailed description:
FIG. 1 is a diagram of a calibration apparatus of the present invention;
FIG. 2 is a flow chart of calibration of the calibration cylinder of the present invention.
Detailed Description
The following description of the embodiments of the present invention is provided for illustrative purposes, and other advantages and effects of the present invention will become apparent to those skilled in the art from the present disclosure.
Example one
Please refer to fig. 1-2. The invention provides a technical scheme that: a manual calibration method for a human body respiratory flow test comprises the following steps:
step one, collecting differential pressure values corresponding to different respiratory flow rates;
extracting a pressure difference value, and establishing a piecewise linear nonlinear relation between the pressure difference value and a flow coefficient under different flow velocities;
and step three, calculating calibration coefficients under other flow velocities according to the piecewise linearity in the nonlinear relation in the step two, and completing flow calibration.
Through the steps, the respiratory flow rate is different flow rate data under the respiratory standard condition, the airflow formed by the flow rate generates pressure difference through the preferred pitot tube pressure difference sensor head, meanwhile, the segmented nonlinear relation of the coefficient element in the flow sensor collecting circuit is collected, calculated and calibrated through the preferred upper computer and kept in the system, and when a user uses the system, the accurate calibration of the whole testing system can be completed through inputting volume calibration data based on the factory calibration nonlinear relation; through the factory subsection calibration of the nonlinear coefficient relation, the actual calibration process of the user is simplified, and the calibration precision is improved.
In order to better realize accurate acquisition of the respiratory flow rate, the respiratory flow rate in the step one is a flow rate under a simulated respiratory flow.
In the embodiment, the error precision can be effectively adjusted by using the standard breathing simulator which is preferably verified, so that the measurement requirement on the differential pressure value is met.
For better determination of the flow rate information, the flow rate is the volume of fluid passing through the flow cross section per unit time.
In this embodiment, the volume of the fluid passing through the flow cross section per unit time is a variable value.
In order to better realize the division of the flow rate, the flow rate comprises flow rate intervals which are arranged from small to large.
In order to better implement the establishment of the nonlinear relationship, the establishing of the nonlinear relationship in the second step includes:
and respectively calculating the proportional relation between the coefficient in each flow velocity interval and the coefficients in other different flow velocity intervals according to the measured pressure difference value and the standard flow velocity.
Preferably, the flow rate interval includes at least a low speed, a medium-low speed, a medium-high speed, and a high speed.
It is to be noted that, when the flow rate calibration is performed by taking the flow rate intervals of low speed, medium and low speed, medium and high speed as examples, the mass conservation law and the energy conservation law (bernoulli equation) are used to obtain the following parameters for the same gas: the dynamic pressure (i.e., differential pressure value) is equal to the total pressure-static pressure, and the corresponding formula for deriving the differential pressure and the flow rate is:
the method is simplified as follows:
wherein v is the speed of exhalation or inhalation; k is the differential pressure generator coefficient; k is a calibration coefficient; ρ is the gas density.
According to the formula, the delta P is the AD value measured by the differential pressure sensor, and the proportional relation between the coefficient at each flow velocity and the other 4 flow velocities is calculated according to the measured differential pressure and the standard flow velocity.
It is also worth noting that the error in this formula mainly comes from the density change of the gas during the flow process, and this error can be reduced by the method of multi-stage calibration, and the coefficients of each flow rate stage can be approximately regarded as a linear relationship, and assuming low speed (50ml/s-500ml/s), medium and low speed (500ml/s-2L/s), medium speed (2L/s-6L/s), medium and high speed (6L/s-12L/s), and high speed (12L/s-16L/s), then the average value of the low speed calibration coefficients of 50 ml/coefficient K50 and 500ml/s coefficient K500 can be approximately calculated, and the coefficients of push and pull are found, i.e., K1 ═ K50+ K500)/2, K1 ═ K '50 + K' 500/2, similarly, medium and low speed K2, K2 ', medium speed K3, K3', medium and high speed K4, K ', high speed K5, K5' can be calculated, and a coefficient K11 at each flow rate is calculated according to the measured pressure difference and the standard flow rate, for example, if the current pressure difference value in the process of pushing the calibration cylinder is in a low speed section, namely Δ P50< Δ P500, then a medium and low speed calibration coefficient K12 ═ K11 ═ K2/K1 can be sequentially calculated through the previously calibrated coefficients, the medium and high speed calibration coefficient K13 ═ K11 ═ K3/K1, the medium and high speed calibration coefficient K82 14 ═ K8456 ═ K4/K1, and the high speed calibration coefficient K15 ═ K36 11 ═ K5/K1; the current differential pressure value is assumed to be in a medium and low speed section, namely Δ P500< Δ P52, the low speed calibration coefficient K12 is K11 × K1/K2, the medium speed calibration coefficient K13 is K11 × K3/K2, the medium and high speed calibration coefficient K14 is K11 × K4/K2, and the high speed calibration coefficient K15 is K11 × K5/K2; the logic calculates other 4 calibration coefficients K12, K13, K14 and K15, and similarly calculates other 4 calibration coefficients K12 ', K13,' K14 and 'K15' of the pull calibration cylinder.
In this embodiment, by dividing the reasonable flow rate intervals, a coefficient relationship can be conveniently established in each flow rate interval.
To further facilitate simple volume calibration by the user, the acquisition of the other flow rates comprises:
and collecting the fluid volume calibration data pushed and pulled once by the standard 3L calibration cylinder, and transmitting the data to the system.
When other flow velocity collection is carried out, a user can finish the collection of the flow volume calibration data only by simply pushing and pulling the 3L calibration cylinder once, and the convenience of field user calibration operation is improved.
It should be noted that, during calibration, as shown in fig. 1 and 2, a standard 3L calibration cylinder is prepared by a user, and the actual error sources during calibration include density variation caused by air temperature and humidity, and nonlinear errors of a pitot tube and a pressure sensor, where the former error is changed by each test scenario of the user, and the latter nonlinear error is related to sensor hardware and is basically determined after leaving the factory. Therefore, the invention mainly aims to use piecewise linearity to represent the latter nonlinear error, and obtain the relationship between piecewise linearity coefficients before the instrument leaves factory, so that when the instrument is used by a client, the calibration barrel is only required to be pushed and pulled once, accurate calibration can be realized, user operation is simplified, the calibration barrel can be directly pushed and pulled once at uniform speed through 3L, the upper computer software determines the current flow velocity section according to the pressure difference value of the pulling and pulling, the integral of the flow velocity to the sampling point is 3L of the volume of the calibration barrel, therefore, the calibration coefficients K11 and K11' of the pushing and pulling at the moment can be calculated through the upper computer software 4, and the derivation process is as follows:
the flow rate is the amount of fluid passing through the cross-section of the pipe per unit time, which is an instantaneous amount, expressed as Qv, and the volume is the cumulative flow rate, which is the total amount of fluid passing through the cross-section of the pipe over a period of time, which is the integral of the fluid over time, expressed as V, thus obtaining the formula for calculating the volume:
the volume V is equal to the volume 3L of the calibration cylinder, and is thus based on the formula
And the integral of the pressure difference value delta P in the process of drawing the calibration cylinder is calculated through the integral, and finally K11 is calculated, and the coefficient K11' in the process of pushing the calibration cylinder can be calculated in the same way.
It is also worth noting that the range to which the current differential pressure value belongs determines which flow velocity segment the calibration belongs, for example, assuming that the current differential pressure value is in the low velocity segment during the pushing of the calibration cylinder, i.e., Δ P50<ΔP<Δ P500, then, the medium-speed and low-speed calibration coefficients K12 ═ K11 × K2/K1, the medium-speed calibration coefficient K13 ═ K11 × K3/K1, the medium-speed and high-speed calibration coefficients K14 ═ K11 × K4/K1, and the high-speed calibration coefficient K15 ═ K11 × K5/K1 can be sequentially calculated through the previously calibrated coefficients; suppose that the current differential pressure value is in the medium-low speed section, i.e. Δ P500<ΔP<Δ P52, a low-speed calibration coefficient K12 ═ K11 ═ K1/K2, a medium-speed calibration coefficient K13 ═ K11 ═ K3/K2, a medium-high-speed calibration coefficient K14 ═ K11 ═ K4/K2, and a high-speed calibration coefficient K15 ═ K11 ═ K5/K2; the other 4 flow rate calibration coefficients K12, K13, K14 and K15 can be calculated according to the logic, and similarly, the other 4 flow rate calibration coefficients K12 ', K13, ' K14 ' and ' K15 ' of the pull calibration cylinder can be calculated according to the calibration calculation, so that the volume calculation of the actual breath is as follows:
example two
The invention also provides a manual calibration system for testing the respiratory flow of the human body, which is characterized by comprising the following components:
the breath flow rate simulation module is used for simulating differential pressure values of different breath flows at corresponding flow rates;
the data storage module is used for establishing and storing a nonlinear relation of piecewise linearity between flow coefficients under different flow velocities; and
and the flow calibration module is used for acquiring volume calibration data and acquiring a calibration coefficient under nonlinear relation piecewise linearity.
In the above embodiment, a manual calibration device for human respiratory flow test is further provided, as shown in fig. 1, including a standard respiratory simulator 1, a differential pressure sensor generator 2, a differential pressure sensor acquisition circuit 3, and an upper computer calibration software 4; the differential pressure sensor acquisition circuit 3 and the upper computer calibration software 4 are connected to the differential pressure sensor generator 2 through the standard respiration simulator 1.
The standard respiration simulator 1 can respectively establish the simulation of expiration and inspiration at the constant speed of 50ml/S, 500ml/S, 2L/S, 6L/S, 12L/S and 16L/S, and the pressure difference values delta P50, delta P500, delta P2, delta P6, delta P12 and delta P16 of each speed of the pressure difference sensor 2 are recorded through the pressure difference sensor acquisition circuit 3 and the upper computer software.
The foregoing embodiments are merely illustrative of the principles and utilities of the present invention and are not intended to limit the invention. Any person skilled in the art can modify or change the above-mentioned embodiments without departing from the spirit and scope of the present invention. Accordingly, it is intended that all equivalent modifications or changes which can be made by those skilled in the art without departing from the spirit and technical spirit of the present invention be covered by the claims of the present invention.
Claims (8)
1. A manual calibration method for a human body respiratory flow test is characterized by comprising the following steps:
step one, collecting differential pressure values corresponding to different respiratory flow rates;
extracting a pressure difference value, and establishing a piecewise linear nonlinear relation between the pressure difference value and a flow coefficient under different flow velocities;
and step three, calculating calibration coefficients under other flow velocities according to the piecewise linearity in the nonlinear relation in the step two, and completing flow calibration.
2. The manual calibration method for the human respiratory flow test according to claim 1, wherein the respiratory flow rate in the first step is a flow rate under a simulated respiratory flow.
3. The manual calibration method for the human respiratory flow test according to claim 1 or 2, wherein the flow rate is a volume of fluid passing through the flow cross section in a unit time.
4. The manual calibration method for the human respiratory flow test according to claim 3, wherein the flow rate comprises flow rate intervals which are arranged from small to large.
5. The manual calibration method for the human respiratory flow test according to claim 4, wherein the establishing the nonlinear relationship in the second step comprises:
and respectively calculating the proportional relation between the coefficient in each flow velocity interval and the coefficients in other different flow velocity intervals according to the measured pressure difference value and the standard flow velocity.
6. The manual calibration method for the human respiratory flow test according to claim 4, wherein the flow rate interval at least comprises a low speed, a medium-low speed, a medium-high speed and a high speed.
7. The manual calibration method for the human respiratory flow test according to claim 3, wherein the acquisition of the other flow rates comprises:
and collecting the fluid volume calibration data pushed and pulled once by the standard 3L calibration cylinder, and transmitting the data to the system.
8. The utility model provides a manual calibration system of human respiratory flow test which characterized in that includes:
the breath flow rate simulation module is used for simulating differential pressure values of different breath flows at corresponding flow rates;
the data storage module is used for establishing and storing a nonlinear relation of piecewise linearity between flow coefficients under different flow velocities; and
and the flow calibration module is used for acquiring volume calibration data and acquiring a calibration coefficient under nonlinear relation piecewise linearity.
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