CN107242874B - Flow sensor for measuring lung function, lung function tester and application - Google Patents
Flow sensor for measuring lung function, lung function tester and application Download PDFInfo
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- 230000004199 lung function Effects 0.000 title claims abstract description 52
- 238000001514 detection method Methods 0.000 claims abstract description 37
- 230000009325 pulmonary function Effects 0.000 claims description 16
- 238000000034 method Methods 0.000 claims description 14
- 238000005259 measurement Methods 0.000 claims description 8
- 230000029058 respiratory gaseous exchange Effects 0.000 claims description 7
- 238000006243 chemical reaction Methods 0.000 claims description 3
- 238000012545 processing Methods 0.000 claims description 3
- 230000003434 inspiratory effect Effects 0.000 claims 1
- 238000012937 correction Methods 0.000 abstract description 7
- 238000012423 maintenance Methods 0.000 abstract description 3
- 238000010586 diagram Methods 0.000 description 9
- 230000035945 sensitivity Effects 0.000 description 7
- 238000005070 sampling Methods 0.000 description 6
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Chemical compound O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 6
- 238000004519 manufacturing process Methods 0.000 description 4
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 3
- 238000013461 design Methods 0.000 description 3
- 239000007789 gas Substances 0.000 description 3
- 210000004072 lung Anatomy 0.000 description 3
- 229910052760 oxygen Inorganic materials 0.000 description 3
- 239000001301 oxygen Substances 0.000 description 3
- 208000000884 Airway Obstruction Diseases 0.000 description 2
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 2
- 210000001015 abdomen Anatomy 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
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- 230000002457 bidirectional effect Effects 0.000 description 1
- 230000000903 blocking effect Effects 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 230000009977 dual effect Effects 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 230000002349 favourable effect Effects 0.000 description 1
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- 239000002207 metabolite Substances 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 230000004202 respiratory function Effects 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
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- A61B5/087—Measuring breath flow
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Abstract
The invention provides a flow sensor for measuring lung function, application of the flow sensor in a lung function measuring instrument and a lung function detection method. The flow sensor is of a hollow pipe structure and is mainly formed by sequentially connecting an expiration air inlet part, a first cone part, a laryngeal part and a second cone part, a low-pressure taking port is formed in the pipe wall of the laryngeal part, and a first high-pressure taking port and a second high-pressure taking port are formed in the pipe walls of two sides of the non-laryngeal part respectively. The flow sensor and the lung function measuring instrument can detect the two-way flow of expiration and inspiration, the structure is compact, the miniaturization of the lung function measuring instrument is facilitated, the calibration and the correction of the instrument are convenient, and the after-sale maintenance is simple.
Description
Technical Field
The invention relates to the field of medical equipment, in particular to a flow sensor for measuring lung function, a lung function tester, application of the flow sensor and a measuring method of the lung function tester.
Background
The functions of the organs of the human body can be normally operated only under the condition of sufficient oxygen supply. Oxygen supply to the human body is obtained entirely by respiration of the lungs, during which the lungs ingest oxygen and expel the metabolite carbon dioxide. The respiratory function of the tester can be judged by utilizing the lung function measurement, and the method has practical clinical significance in the aspects of identifying the type of airway obstruction, evaluating the lung function before chest and abdomen surgery and the like.
With the progress of technology, the pulmonary function tester has gradually developed from the traditional float-type rotary type electronic tester which is convenient to carry. In such electronic pulmonary function testers, the respiratory flow sensor is one of its key components.
As shown in fig. 1, the differential pressure flow sensor designed by the venturi tube principle comprises two pressure taking ports (double-hole flow sensor), wherein a low pressure taking port 1001 is arranged at a throat part 1003, and a high pressure taking port 1002 is arranged at an exhalation air inlet part 1004. When the exhalation parameters are detected, the air flow passes through the high-pressure taking port and then enters the low-pressure taking port of the laryngeal part, and as the aperture of the laryngeal part is small, the air flow is compressed and accelerated, the pressure loss is relatively large, and the flow rate is reduced, but the high-pressure taking port is arranged in front of the laryngeal part, so that the flow rate testing precision is not influenced. If the flow sensor is used for detecting the inspiration parameter, the airflow can firstly pass through the low-pressure taking port of the laryngeal part, the airflow pressure loss and the flow drop, and then enter the high-pressure taking port, and the detected flow can be obviously smaller, so that the differential pressure type flow sensor based on the venturi tube principle cannot detect the expiration and inspiration bidirectional flow simultaneously by using the two pressure taking holes.
In order to detect the two-way flow of exhaling and inhaling at the same time, as shown in fig. 2, the design of adopting venturi tube principle to design differential pressure type flow sensor adopts the design of four pressure taking ports, a high pressure taking port 1002 needs to be added to the inhaling air inlet 1005, a low pressure taking port 1001 is added to the laryngeal, the length of the laryngeal 1003 is necessarily increased, the length of the whole flow sensor is increased, the pressure taking ports are more, the structure is complex, and the miniaturization of the detecting instrument is not facilitated.
As shown in FIG. 3, the gas flow sensor designed by adopting the orifice plate principle has small gas flow pressure loss due to the fact that the thickness of the orifice plate 1006 is smaller than 0.02D (the diameter of a pipe), and the accuracy of detecting the two-way flow of expiration and inspiration is not affected. However, since the inhalation flow rate of the human body is much smaller than the exhalation flow rate, two sets of pressure taking ports are used to detect the exhalation flow rate and the inhalation flow rate simultaneously, and thus the sensitivity of inhalation detection is insufficient, four pressure taking ports 1007 are used, and two differential pressure sensors 1008 are included, a high-range differential pressure sensor and a low-range differential pressure sensor, the high-range differential pressure sensor is used to detect the exhalation flow rate, and the low-range differential pressure sensor is used to detect the inhalation flow rate, so as to improve the inhalation flow rate detection sensitivity. However, due to the adoption of two groups of differential pressure sensors with different measuring ranges, when the flow sensor is calibrated, two groups of calibration systems are needed, so that the complexity of the instrument is increased, the reliability is reduced, and the production procedure, the manufacturing cost and the complexity of after-sales maintenance are increased.
Disclosure of Invention
In order to overcome the above-mentioned drawbacks, the present invention provides a flow sensor for measuring pulmonary function, which is of a hollow tube structure and is mainly formed by sequentially connecting an exhalation air inlet part, a first cone part, a laryngeal part and a second cone part, wherein a low-pressure taking port is formed on the tube wall of the laryngeal part, and a first high-pressure taking port and a second high-pressure taking port are respectively formed on the tube walls at two sides of the non-laryngeal part.
Further, the expiratory air inlet and the laryngeal portion are cylindrical, the expiratory air inlet is larger than the laryngeal portion, the first cone portion and the second cone portion are in a truncated cone shape, and the smaller end of the first cone portion and the smaller end of the second cone portion face the laryngeal portion respectively.
Further, the first pressure taking port is formed in the first cone portion or the expiratory air inlet portion, and the second high pressure taking port is formed in the second cone portion.
Preferably, the distance between the first high-pressure taking port and the low-pressure taking port is smaller than the distance between the second high-pressure taking port and the low-pressure taking port.
The invention also provides a lung function tester, which comprises a differential pressure sensor and a flow sensor, wherein the flow sensor is of a hollow pipe structure and is mainly formed by sequentially connecting an expiration air inlet part, a first cone part, a laryngeal part and a second cone part, a low-pressure taking port is formed in the pipe wall of the laryngeal part, and a first high-pressure taking port and a second high-pressure taking port are respectively formed in the pipe walls at two sides of the non-laryngeal part; the differential pressure sensor includes a first differential pressure sensor and a second differential pressure sensor.
Further, the expiratory air inlet and the laryngeal portion are cylindrical, the expiratory air inlet is larger than the laryngeal portion, the first cone portion and the second cone portion are in a truncated cone shape, and the smaller end of the first cone portion and the smaller end of the second cone portion face the laryngeal portion respectively.
Further, a first high-pressure taking port of the flow sensor is connected with the positive pressure end of the first pressure difference sensor, a second high-pressure taking port is connected with the positive pressure end of the second pressure difference sensor, and the low pressure ends of the two pressure difference sensors are respectively connected with the low-pressure taking ports of the laryngeal part through a three-way pipe.
Further, the pulmonary function analyzer further comprises a microprocessor. The data of the differential pressure sensor is collected and processed by the microprocessor.
Preferably, the pulmonary function analyzer further comprises an automatic judging system for detecting two detection modes of expiration detection and inspiration detection.
The invention also provides a method for determining lung function, which comprises the following steps:
(1) Providing a lung function tester according to the invention;
(2) The tester holds the front end of the expiration air inlet part of the flow sensor, and exhales or inhales;
(3) Reading the first and second differential pressure sensor data;
(4) Judging whether to start expiration or inspiration;
(5) Judging whether the patient is in an expiration state, and if so, taking data of a first differential pressure sensor by a lung function tester; if not, the lung function tester takes the data of the second differential pressure sensor;
(6) The microprocessor of the lung function tester obtains the data of the first or second differential pressure sensor, calculates the air flow;
(7) Obtaining the lung function measurement parameters.
The judging method of the breathing state in the step (4) comprises the following steps: comparing the differential pressure values of the two differential pressure sensors to determine whether the flow sensor is exhaling or inhaling by the tester; or the operator judges whether the flow sensor is breathing out or inhaling according to the current or impending action of the tester.
The flow sensor is applied to the measurement of lung function indexes.
The beneficial effects of the invention are as follows: the flow sensor with one low pressure sampling port and two high pressure sampling ports is favorable for miniaturization of the lung function measuring instrument. And the production procedures are few, and the manufacturing cost is low. The lung function tester adopting the flow sensor can detect the two-way flow of expiration and inspiration at the same time, is convenient for the calibration and correction of the lung function tester, and is beneficial to after-sales maintenance.
Drawings
FIG. 1 is a schematic diagram of a prior art dual orifice flow sensor.
FIG. 2 is a schematic diagram of a prior art four-hole flow sensor.
FIG. 3 is a schematic diagram of a prior art orifice flow sensor.
FIG. 4 is a schematic diagram of a three-hole flow sensor according to the present invention.
Fig. 5 is a schematic diagram of a three-hole flow sensor with an intake air portion.
FIG. 6 is a schematic diagram of a three-hole flow sensor coupled to a differential pressure sensor.
Fig. 7 is a block diagram of the circuit of the pulmonary function tester according to the present invention.
FIG. 8 is a block diagram of an assay process.
Detailed Description
As shown in fig. 4, the flow sensor for measuring lung function is of a hollow tube structure and is mainly formed by sequentially connecting an exhalation air inlet part 1, a first cone part 2, a throat part 3 and a second cone part 4, a low-pressure taking opening 5 is formed in the tube wall of the throat part, and a first high-pressure taking opening 6 and a second high-pressure taking opening 7 are respectively formed in the tube walls on two sides of the non-throat part. The expiratory air inlet part 1 and the laryngeal part 3 are cylindrical, and the diameter of the expiratory air inlet part is larger than that of the laryngeal part. The first cone part 2 and the second cone part 4 are in a truncated cone shape, and the smaller ends of the first cone part and the second cone part face the laryngeal opening respectively.
The first pressure taking port 6 can be formed on the first cone part 2 or the exhalation air inlet part 1. The second high-pressure tap 7 may be provided at the second cone 4. As shown in fig. 5, in the embodiment in which the larger end of the second taper portion is connected to the intake air portion 8, the second high-pressure intake port 7 may also be opened in the intake air portion 8. When the lung function parameter at the time of expiration is measured, the pressure difference between the first high-pressure taking port and the low-pressure taking port is measured by the pressure difference sensor. When the lung function parameter at the time of inhalation is measured, the pressure difference between the second high-pressure taking port and the low-pressure taking port is measured by the pressure difference sensor. The lung function tester calculates and analyzes various lung function indexes of the tester according to the pressure difference between the high pressure sampling port and the low pressure sampling port, and provides the lung function indexes for doctors or testers to judge illness state or confirm curative effect.
In the embodiment of the flow sensor in which parameters such as the maximum diameter of the pipe body, the length of the pipe body, the first cone angle theta 1 and the second cone angle theta 2 are fixed, the sensitivity required in the exhalation measurement is obtained by adjusting the distance between the first high-pressure taking port and the low-pressure taking port, and the sensitivity required in the inhalation measurement is obtained by adjusting the distance between the second high-pressure taking port and the low-pressure taking port.
In the embodiment where the pressure point of the differential pressure sensor is fixed, that is, the distance between the high-pressure tap and the low-pressure tap of the flow sensor matched with the pressure point is fixed, the detection range required in the breath measurement is obtained by adjusting the diameter of the exhalation air inlet part, the diameter of the laryngeal part, the first cone angle theta 1 and the length thereof, or the second cone angle theta 2 and the length thereof of the flow sensor.
Since the maximum flow rate of exhalation detected by the lung function is much larger than the maximum flow rate of inhalation, the pressure of the second high-pressure taking port needs to be increased in order to improve the sensitivity of inhalation flow rate detection. According to the fluid dynamics Bernoulli principle, the relation between the flow and the pressure difference satisfies the formula (I), wherein D is the diameter of the low-pressure taking port of the throat part, D is the diameter of the second high-pressure taking port of the air suction and air inlet part, and ρ is the density of the fluid. When D becomes larger, the differential pressure Δp corresponding to a certain flow rate becomes correspondingly larger.
(I)
In a specific embodiment, the distance between the second high-pressure taking port 7 and the low-pressure taking port 5 is increased, so that the second high-pressure taking port is opened at the larger aperture of the second cone portion 4, and the pressure difference output corresponding to the suction flow is increased. The positions of the first high-pressure taking port and the second high-pressure taking port are adjusted, so that the flow detection of expiration and inspiration meets the requirements of measuring range and sensitivity, the differential pressure detection measuring range of the expiration differential pressure sensor and the inspiration differential pressure sensor is consistent, namely the differential pressure sensor with the same model can be used, the calibration and correction of the differential pressure sensor adopt the same method, and the value range of the correction coefficient is consistent. Thus facilitating calibration and correction of the pulmonary function meter.
The humidity of the gas exhaled by the human body is high, water vapor is easy to condense in the flow sensor, in order to prevent the condensed water from blocking the pressure taking opening, in a specific embodiment, the aperture of the pressure taking opening is 1.0-1.5 mm, the condensed water is prevented from flowing into the pressure taking opening by using the surface tension of the water, and meanwhile, the high-pressure taking opening is arranged on the cone part, so that the condensed water can flow outwards without staying at the pressure taking opening, the throat part is as short as possible, for example, less than 6mm, and the water vapor is ensured not to stay at the throat part.
As shown in fig. 6, the pulmonary function tester includes a differential pressure sensor and a flow sensor according to the present invention. The first high-pressure taking port 6 of the first cone part of the flow sensor is connected with the positive pressure end 103 of the first differential pressure sensor 101, the second high-pressure taking port 7 of the second cone part is connected with the positive pressure end 103 of the second differential pressure sensor 102, and the low-pressure ends 104 of the two differential pressure sensors are respectively connected with the low-pressure taking ports 5 of the laryngeal part through three-way pipes 105.
The differential pressure sensor can be connected with the microprocessor 106, and the microprocessor is used for collecting and processing signals of the differential pressure sensor, calculating and analyzing various functional indexes of the lung of the tester according to the differential pressure between the high pressure sampling port and the low pressure sampling port, and taking the functional indexes as reference indexes of the current physical condition or treatment effect of the tester. The microprocessor may be self-contained with the pulmonary function tester or may be an external device, such as a computer, etc.
The lung function tester also comprises an automatic judging system for detecting two detection modes, namely expiration detection and inspiration detection. When the airflow in the flow sensor is the expiratory airflow, the data of the first differential pressure sensor is used for measuring the differential pressure between the first high-pressure taking port and the low-pressure taking port, so as to obtain the lung function parameter during expiration. When the air flow in the flow sensor is the inspiration air flow, the data of the second pressure difference sensor is used for measuring the pressure difference between the second high-pressure taking port and the low-pressure taking port, so as to obtain the lung function parameter during inspiration.
The automatic breath and inspiration judging system can be part of a program in lung function detection software, and can realize switching between breath detection and inspiration detection through program control. The automatic judgment system can be freely switched between the exhalation detection mode and the inhalation detection mode rapidly, especially when continuous detection of inhalation or exhalation is required.
When the exhalation parameters are detected, the air flow passes through the first high-pressure taking port and then enters the low-pressure taking port of the laryngeal part, the air flow is compressed and accelerated due to the small aperture of the laryngeal part, the pressure loss flow is reduced, and finally the air flow passes through the second high-pressure taking port, so that the pressure difference detection value of the first pressure difference sensor is always larger than that of the second pressure difference sensor; when the air suction parameters are detected, the air flow passes through the second high-pressure taking port and then enters the low-pressure taking port of the laryngeal part, the air flow is compressed and accelerated, the pressure loss flow is reduced, and finally passes through the first high-pressure taking port, so that the pressure difference detection value of the second pressure difference sensor is always larger than that of the first pressure difference sensor. Thus, in a specific embodiment, the automatic breath-and-inhalation judging system judges whether the current tester exhales or inhales by comparing the differential pressure values of the two differential pressure sensors, and the tester automatically switches to the corresponding breath detection mode or inhalation detection mode according to the judging result.
Fig. 7 is a schematic circuit diagram of the pulmonary function tester of fig. 6, including first and second differential pressure sensors, a signal amplifying circuit, a two-channel a/D conversion circuit, a microprocessor circuit, a display screen, a power management circuit, a power supply, and keys. When the device is used, a user presses a key to start lung function detection, the tester continuously exhales and inhales to the flow sensor, the pressure difference sensor amplifies the measured signal, digital-to-analog conversion is carried out on the amplified signal, the amplified signal is sent to the microprocessor for processing, and the processed related information is displayed on the display screen. The power supply supplies power to the units through the power supply management circuit.
As shown in fig. 8, a method for determining lung function comprises the steps of:
(1) Providing a lung function tester according to the invention;
(2) The tester holds the front end of the expiration air inlet part of the flow sensor, and exhales or inhales;
(3) Reading the first and second differential pressure sensor data;
(4) Judging whether to start expiration or inspiration;
(5) Judging whether the patient is in an expiration state, and if so, taking data of a first differential pressure sensor by a lung function tester; if not, the lung function tester takes the data of the second differential pressure sensor;
(6) The microprocessor of the lung function tester obtains the data of the first or second differential pressure sensor, calculates the air flow;
(7) Obtaining the lung function measurement parameters.
The method for judging the breathing state in the step (5) comprises the following steps: comparing the differential pressure values of the two differential pressure sensors to determine whether the flow sensor is exhaling or inhaling by the tester; or the operator judges whether the flow sensor is breathing out or inhaling according to the current or impending action of the tester.
The flow sensor or the lung function tester can be applied to routine physical examination, athlete physical examination, daily monitoring of asthmatic patients, identification of airway obstruction type, lung function evaluation before chest and abdomen surgery and the like.
Example 1
The experimental group is the flow sensor provided by the invention, the diameter of an expiration air inlet part is 27mm, the cone angle of a first cone part is 40 degrees, the diameter of a laryngeal opening is 12mm, the cone angle of a second cone part is 25.4 degrees, and the diameter of an inspiration air inlet part is 27mm. The distance between the first high-pressure taking port and the low-pressure taking port is 20mm, and the distance between the second high-pressure taking port and the low-pressure taking port is 25mm.
The control group is a double-hole flow sensor in the prior art, the diameter of an expiration air inlet part is 27mm, the cone angle of a first cone part is 40 degrees, the diameter of a laryngeal opening is 12mm, the cone angle of a second cone part is 25.4 degrees, and the diameter of an inspiration air inlet part is 27mm. The distance between the first high-pressure taking port and the low-pressure taking port is 20mm.
The flow sensors of the experimental group and the flow sensors of the control group are compared with the standard flow sensors for detection, and the detection results are shown in tables 1 and 2.
Table 1 experimental group flow sensor breath and inspiration experimental data
| Standard flow value (L/min) | Expiration detection value (L/min) | Error (%) | Standard flow value (L/min) | Inhalation detection value (L/min) | Error (%) | |
| 50 | 49.5 | -1.0 | 30 | 29.6 | -1.3 | |
| 80 | 78.8 | -1.5 | 40 | 39.7 | -0.7 | |
| 120 | 118 | -1.7 | 50 | 49.6 | -0.8 | |
| 180 | 179 | -0.6 | 60 | 59.9 | -0.2 | |
| 250 | 248 | -0.8 | 80 | 79.3 | -0.9 | |
| 350 | 350 | 0.0 | 100 | 99.5 | -0.5 | |
| 400 | 401 | 0.3 | 120 | 119 | -0.8 | |
| 450 | 452 | 0.4 | 180 | 179 | -0.6 | |
| 500 | 503 | 0.6 | 250 | 249 | -0.4 | |
| 550 | 553 | 0.5 | 350 | 351 | 0.3 | |
| 600 | 606 | 1.0 | 400 | 400 | 0.0 | |
| 700 | 712 | 1.7 | 450 | 451 | 0.2 | |
| 800 | 809 | 1.1 | 500 | 502 | 0.4 |
Table 2 control flow sensor breath-in experimental data
| Standard flow value (L/min) | Expiration detection value (L/min) | Error (%) | Standard flow value (L/min) | Inhalation detection value (L/min) | Error (%) | |
| 50 | 49.6 | -0.8 | 30 | 17.9 | -40.3 | |
| 80 | 78.5 | -1.9 | 40 | 23.6 | -41.0 | |
| 120 | 119 | -0.8 | 50 | 32.7 | -34.6 | |
| 180 | 179 | -0.6 | 60 | 43.5 | -27.5 | |
| 250 | 249 | -0.4 | 80 | 71.9 | -10.1 | |
| 350 | 352 | 0.6 | 100 | 92.6 | -7.4 | |
| 400 | 399 | -0.3 | 120 | 113 | -5.8 | |
| 450 | 451 | 0.2 | 180 | 173 | -3.9 | |
| 500 | 502 | 0.4 | 250 | 241 | -3.6 | |
| 550 | 555 | 0.9 | 350 | 333 | -4.9 | |
| 600 | 607 | 1.2 | 400 | 387 | -3.3 | |
| 700 | 709 | 1.3 | 450 | 427 | -5.1 | |
| 800 | 813 | 1.6 | 500 | 473 | -5.4 |
From the above experimental detection data, it can be seen that the flow sensor of the present invention has higher detection sensitivity and accuracy when used for detecting lung function than the sensors of the control group (prior art), and the result is better than that of the control group especially when used for detecting inspiration.
Example 2
Measuring the maximum pressure difference of the flow sensor of the experimental group of the embodiment 1, wherein the maximum range of the expiratory flow is 900L/min, and the maximum flow corresponds to the pressure difference of 10kPa; the maximum suction flow is 600L/min, and the maximum suction flow corresponds to a pressure difference of 10kPa. Thus the first differential pressure sensor and the second differential pressure sensor may use the same range of differential pressure sensors. The two sensors were calibrated by experimental testing of flow and differential pressure data (see table 3). In specific correction, two differential pressure sensors are connected in parallel and apply the same differential pressure, and two differential pressure points of 1kPa and 5kPa are respectively taken for linear correction.
TABLE 3 Table 3
| Respiratory airflow value (L/min) | First differential pressure sensor (kPa) | Air flow value (L/min) | Second differential pressure sensor (kPa) | |
| 50 | 0.03 | 50 | 0.07 | |
| 100 | 0.12 | 100 | 0.27 | |
| 200 | 0.48 | 150 | 0.6 | |
| 300 | 1.08 | 200 | 1.07 | |
| 400 | 1.93 | 250 | 1.68 | |
| 500 | 3.02 | 300 | 2.42 | |
| 600 | 4.35 | 350 | 3.29 | |
| 700 | 7.36 | 400 | 4.3 | |
| 800 | 7.74 | 500 | 6.73 | |
| 900 | 9.8 | 600 | 9.7 |
Claims (10)
1. A flow sensor for lung function survey, be hollow tube structure, by exhaling inlet portion, first cone portion, laryngeal portion and second cone portion link to each other in proper order and form, its characterized in that, low pressure is got the pressure mouth and is offered on the pipe wall of laryngeal portion, and first high pressure is got the pressure mouth and second high pressure is got the pressure mouth and is offered respectively on the pipe wall of non-laryngeal portion both sides, and first high pressure is got the pressure mouth and is offered at first cone portion, and second high pressure is got the pressure mouth and is offered at second cone portion, and distance between first high pressure is got the pressure mouth and the low pressure is got the pressure mouth and is got the distance between the pressure mouth with the low pressure to get the pressure mouth to first high pressure.
2. The flow sensor of claim 1, wherein the exhalation intake portion and the laryngeal portion are cylindrical, the diameter of the exhalation intake portion is greater than the diameter of the laryngeal portion, the first cone portion and the second cone portion are frustoconical, and the smaller diameter ends of the first cone portion and the second cone portion face the laryngeal portion, respectively.
3. The flow sensor of claim 1, wherein the distance between the first high pressure inlet and the low pressure inlet and the distance between the second high pressure inlet and the low pressure inlet are set such that the differential pressure detection ranges of the expiratory differential pressure sensor and the inspiratory differential pressure sensor are consistent.
4. A flow sensor according to claim 3, wherein the exhalation inlet portion has a diameter of 27mm, the taper angle of the first taper portion is 40 degrees, the throat portion has a diameter of 12mm, the taper angle of the second taper portion is 25.4 degrees, the inhalation inlet portion has a diameter of 27mm, the first high pressure tap is 20mm from the low pressure tap, the second high pressure tap is 25mm from the low pressure tap, and the tap aperture is 1.0 to 1.5mm.
5. The lung function tester comprises a differential pressure sensor and a flow sensor, and is characterized in that the flow sensor is of a hollow pipe structure and is formed by sequentially connecting an expiration air inlet part, a first cone part, a laryngeal part and a second cone part, a low-pressure taking port is formed in the pipe wall of the laryngeal part, a first high-pressure taking port and a second high-pressure taking port are respectively formed in the pipe walls on two sides of the non-laryngeal part, the first high-pressure taking port is formed in the first cone part, and the second high-pressure taking port is formed in the second cone part; the differential pressure sensor comprises a first differential pressure sensor and a second differential pressure sensor, a first high-pressure taking port of the flow sensor is connected with the positive pressure end of the first differential pressure sensor, a second high-pressure taking port of the flow sensor is connected with the positive pressure end of the second differential pressure sensor, the low pressure ends of the two differential pressure sensors are respectively connected with the low-pressure taking port of the laryngeal part through a three-way pipe, and the distance between the first high-pressure taking port and the low-pressure taking port is smaller than the distance between the second high-pressure taking port and the low-pressure taking port.
6. The pulmonary function analyzer of claim 5, wherein the distance between the first high pressure port and the low pressure port is set to match the differential pressure sensing ranges of the first differential pressure sensor and the second differential pressure sensor.
7. The pulmonary function analyzer of claim 5, further comprising a signal amplifying circuit, a dual-channel a/D conversion circuit, a microprocessor, a display screen, a power management circuit, a power supply and a key, wherein the differential pressure sensor amplifies the measured signal, digital-to-analog converts the amplified signal, and sends the amplified signal to the microprocessor for processing, and the processed related information is displayed on the display screen.
8. A method of pulmonary function determination comprising the steps of:
(1) Providing a pulmonary function tester of any one of claims 5 to 7;
(2) The tester holds the front end of the expiration air inlet part of the flow sensor, and exhales or inhales;
(3) Reading the first and second differential pressure sensor data;
(4) Judging whether to start expiration or inspiration;
(5) Judging whether the patient is in an expiration state, and if so, taking data of a first differential pressure sensor by a lung function tester; if not, the lung function tester takes the data of the second differential pressure sensor;
(6) The microprocessor of the lung function tester obtains the data of the first or second differential pressure sensor, calculates the air flow;
(7) Obtaining the lung function measurement parameters.
9. The method of determining pulmonary function according to claim 8, wherein the method of determining the breathing state in step (4) is selected from the group consisting of: comparing the differential pressure values of the two differential pressure sensors to judge whether the flow sensor is used for exhaling or inhaling by the testers, wherein the judging method is that the exhaling detection is judged when the differential pressure detection value of the first differential pressure sensor is larger than the differential pressure detection value of the second differential pressure sensor; when the pressure difference detection value of the second pressure difference sensor is larger than that of the first pressure difference sensor, judging that the air suction detection is carried out; or the operator judges whether the flow sensor is breathing out or inhaling according to the current or impending action of the tester.
10. Use of a flow sensor according to any one of claims 1 to 4 for determining an index of pulmonary function.
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| PCT/CN2017/099296 WO2018041068A1 (en) | 2016-08-29 | 2017-08-28 | Flow sensor for pulmonary function testing, spirometer and testing method and application thereof |
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| JP6905962B2 (en) * | 2018-07-12 | 2021-07-21 | 日立Astemo株式会社 | Flow sensor |
| CN109984746A (en) * | 2019-04-05 | 2019-07-09 | 浙江亿联康医疗科技有限公司 | Pulmonary function test apparatus detection device |
| CN113558659B (en) * | 2021-07-30 | 2023-07-04 | 重庆安酷科技有限公司 | High-precision ultrasonic lung function detector and detection method thereof |
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| FR2725123B1 (en) * | 1994-09-30 | 1996-12-20 | Soc D Thermoformage Et D Injec | TIP EXPIRATORY FLOW MEASURING APPARATUS |
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