JPS60168433A - Data processing apparatus for measuring nasal cavity ventilation degree - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a data processing device used in a nasal ventilation system for measuring nasal ventilation.

Measuring nasal airflow is useful for diagnosing the degree of nasal breathing disorder (nasal congestion) and selecting its treatment, studying the relationship with the lower respiratory tract, observing the hemodynamics and pathology of the nasal mucosa, determining allergic reactions, and nasal congestion. It is used to evaluate the effectiveness of drug therapy and surgery, and its usefulness is extremely high.

The measurement parameters that express nasal ventilation are:
There are the differential pressure between the two ends of the nasal cavity P1, the amount of air flowing through the nasal cavity (2), the time required to flow a constant amount of air T1, the amount of air per unit time, ie, the flow rate t, etc. The nasal airflow rate may be expressed by the individual values of the above parameters, or may be expressed by the relationship between the above parameters. Currently, the latter is used, and its basis is the differential pressure/flow velocity curve (rhlnorheo).
gram). There are several ways to express the nasal airflow rate from this curve. An example is shown below.

■ Empirical formula of R,ohrer P = K, V -)
-K2<12+ This is a formula derived by Rohrer from airway experiments, which states that the intranasal airflow is mixed with turbulence, so the differential pressure P is expressed by a quadratic formula of the flow rate t. K, (laminar flow coefficient)
Toni2 (turbulence coefficient) can be calculated from the above differential pressure/flow velocity curve.

■Resistance R: This is the force required to flow air at a unit flow rate through the airway, and is expressed as B-P7v. In this case, the larger the value, the worse the air permeability becomes. Moreover, the above Rohrer
From the O type to -1-K, the resistance R increases as the flow rate decreases.

■ Air permeability conductance G: It is the reciprocal of the resistance, and G
It is expressed as -v7P and indicates the amount of air flowing with unit driving force per unit time.

In order to express the nasal airflow rate, it is necessary to detect all of the differential pressure P and flow velocity as described above. A method for detecting such differential pressure P and flow rate will be described below.

■ Comprehensive air permeability measurement method: As shown in Fig. 1, a mask 2 to which a measuring tube 1 is connected is brought into close contact with the subject's face, a guide tube 3 is inserted into the oral cavity, and the mask is held between the teeth and lips. Measuring tube 1
A resistor 4 whose resistance value is known is provided inside. The flow velocity detector 5 detects the flow velocity from the differential pressure at two points along the resistor 4. On the other hand, the differential pressure detector 6 is connected to the guide tube 3 and the measuring tube 1 to detect the entire differential pressure between the external nostril and oropharynx of the subject. If the subject is allowed to breathe through the nose while wearing such an instrument, the differential pressure P and flow velocity (2) necessary for measuring the nasal air permeability can be obtained.

■ Unilateral air permeability measurement method: A method that measures either the left or right nasal cavity of the subject.
ior) Law and Anterior (anterior)
It is divided into law and law.

■ Bosteriol method: The arrangement of the measuring instruments is the same as in Figure 1, but a cotton plug is placed in the external nostril on the non-measuring side. If the subject is allowed to breathe quietly through the nose in this state, the differential pressure P and flow velocity (2) on the nasal cavity side to be measured can be obtained.

■Anterior method: There are two types of this method: the nozzle method and the mask method. In the nozzle method, as shown in Figure 2, the nozzle 8 attached to the measuring tube 7 is lightly inserted into the nostril on the measuring side, and the jet tube 9 is applied to the nostril on the non-measuring side to measure the nasopharyngeal pressure from the front. Differential pressure Pf between this pressure and the external nostril on the measuring side is extracted by differential pressure detection 3-utility 6, while a resistor (not shown) with a known resistance value is installed in the measuring tube 7. ), the flow velocity is detected by a flow velocity detector 5 based on the pressure difference between two points. In the mask method, as shown in FIG.
0 is connected to the subject's face, the nozzle piece 13' is inserted into the nostril on the non-measurement side, and the tube 14 connected to this nozzle piece 13 is connected to the cushion at the edge of the mask 11. Nasopharyngeal pressure is derived from between the face (some models are designed to pass through the mask) and guided from the front, and the difference between this pressure and the pressure in the measurement tube 10 on the mask 11 side is detected by the differential pressure detector 6. On the other hand, this method uses a flow velocity detector 5 to extract the flow velocity by using a pressure difference between two points along a resistor similar to the above-mentioned resistor provided in the measuring tube 10.

Different pressure/flow velocity curves are drawn based on the differential pressure P1 flow velocity summer data obtained by each of these measurement methods to analyze or express the nasal airflow rate, but the comprehensive airflow measurement method This is convenient because it allows you to understand it comprehensively. but,
Even if there is slight stenosis in one nasal cavity, if the ventilation in the other nasal cavity is sufficiently good, the overall value is considered normal, so it is not possible to estimate the difference in ventilation between the left and right nasal cavities. In the one-sided air permeability measurement method, the differential pressure P1 and flow velocity V between the left and right nasal cavities are obtained, so the overall air permeability can be calculated based on these data.

For example, a formula may be used to combine the total resistance value representing the total ventilation rate with the left nasal cavity resistance RR and the right nasal cavity resistance RR. However, conventionally, such calculations have been performed manually. For this reason, it is inconvenient because it takes time and effort to calculate the total air permeability after measuring the air permeability of the left and right nasal passages.

The present invention has been made in view of the above drawbacks, and its purpose is to:
Differential pressure P and flow velocity in the left and right nasal cavities! An object of the present invention is to provide a data processing device for measuring nasal air permeability, which can easily obtain a comprehensive air permeability from data of the nasal cavity in a short time.

Therefore, in the present invention, the differential pressure and flow velocity are measured using differential pressure data corresponding to the differential pressure between the front and rear ends of the left and right nasal cavities of the subject, and flow velocity data corresponding to the flow velocity of the left and right nasal cavities of the subject, respectively. Based on these data, the flow velocity in the left nasal cavity and the flow velocity in the right nasal cavity corresponding to the same predetermined differential pressure are calculated for the left and right nasal cavities, and the flow velocity in the right nasal cavity is calculated based on this calculation result. The above objective is achieved by adding the flow velocity in the left nasal cavity and the flow velocity in the right nasal cavity corresponding to a predetermined differential pressure, and performing various data processing representing the overall nasal cavity ventilation based on the addition result. did.

Hereinafter, an embodiment of the present invention will be described with reference to the drawings.1 FIG. 4 is a diagram for explaining an embodiment of the present invention using a microcomputer. In the figure, numeral 21 is a differential pressure detector, and numeral 21 is a flow rate detector. The differential pressure P2 and the flow velocity (2) in the left and right nasal cavities are applied to the differential pressure detector 21 and the flow velocity detector 21 by one of the above-mentioned one-sided air permeability measuring methods. It is also possible to directly draw a differential pressure/flow velocity curve on the X-Y recorder 22 using the differential pressure P given here as the X coordinate and the flow velocity ViY coordinate. In the device of this embodiment, any data of the given differential pressure P11 flow velocity is selected by the multiplexer, sampled by the sample/hold circuit U, and then A
The data is digitized by a /D converter 25 and processed by a microcomputer 26. The microcomputer 26 has a CPU 27, I (10M28
, R, AM29, (interface 7z-bus 30 and a bus 31 connecting them).

A program for controlling the CPU 27 is written in the ROM 28. According to this program, the CPU 27 exchanges data with the interface 30 or the RAM 29, performs arithmetic processing, and outputs the processed data to the interface as necessary. It functions as each means shown in FIG.

In addition to the above A/D converter 25, the interface 30 includes
A keyboard 32, a cathode ray tube display 33, a printer, and a monitor 35 are connected.

The program written in column 0M28 is shown in a flowchart as shown in FIG. See Figure 6 below.Ii
The operation of this device will be explained below.

First, when the operator of this apparatus confirms that the subject's nasal cavity to be measured is on the right side, he enters data indicating that it is on the "right" side into the microcomputer using the keyboard 32. The CPU 27 stores the information in a predetermined area of the booter RA-M 29. Next, the CPU 27 starts at step 10 on the right side of the flowchart shown in FIG.
1, and when the starting point of one breath shown in the differential pressure/time curve of FIG. 7 is detected, the process proceeds to step 102, where
Data on differential pressure 4 and flow velocity per sec are stored in area M* of RAM 29 specified based on the above “right” data.
't respectively.

This process is continued until the i point (shown in FIG. 7) of one breath is detected in step 103. Next, the CPU 27 proceeds to step 104 and detects the maximum value and minimum value from among the differential pressure PR data stored in area M of the RAM 29, and in step 105, the 0, 01 anH, O, the corresponding time is calculated by interpolation, and the result is stored in area M of the RAM 29. Next, the CPU 27 proceeds to step 106, where the flow velocity v corresponding to the time obtained by the interpolation calculation in step 105 is calculated in the area 8- of the RAM 29 based on the data stored, and the result is RAM
29 area M4. And the CPU 27 is
Proceeding to step 107, the data of the flow velocity destination corresponding to each differential pressure of 0.01 cm H, 0 = area M of the iRAM 29,
Store in.

Assuming that the processing step iA up to this point is the same, the same processing step A' is also performed when measuring the left nasal cavity (the code indicating the area for the left nasal cavity is replaced by the corresponding code on the right side, '
(I will add a dash).

Next, the CPU 27 proceeds to step 108, where the RA
Based on the data stored in the M29 area pigeon, M:, the flow velocity on the left and right is determined every 0.01 cmH20 of the differential pressure? ,V,
-i addition, result? ,-? , +% are stored in area M of the RAM 29. This process is performed from the maximum value of the differential pressure P to the minimum value. CPIJ27 is step 109
If it is determined that the calculation and storage of the results at the minimum value of the differential pressure P have been completed, the process proceeds to step 110, where each differential pressure P (0.01cm) in the range from the maximum value to the minimum value is calculated.
Resistance n, =r>ductor>g, is calculated for each H20) and the result is stored in area M7 of RAM29. Then, in step 111, the CPU 27 selects the keyboard 32.
Based on the data stored in each area of the RAM 29 in the areas 1 to 1, threshold to 1, 2, and 3, the cathode ray tube display 33 and printer 34 display numerical values (print) and waveforms (print) according to instruction data given from f: Do it. For example, when displaying a differential pressure/flow velocity curve on the screen of the cathode ray tube display 33, the operator inputs data to that effect into the microcomputer section using the keyboard 32, and the CPU 27 stores the data in areas M, g, and area of the RAM 29. Read out the data and display it on the cathode ray tube display 3.
Output to 3. In response to these data, the cathode ray tube display 33 displays three curves as shown in FIG.
o) Display in full screen. The measurer can then use this curve to analyze data regarding the left, right, and overall nasal airflow rates.

As explained above, according to the present invention, the total pressure difference and the flow velocity can be immediately calculated by simply applying the pressure difference and flow velocity between the left and right nasal cavities.
A flow velocity curve is obtained. Then, from this overall differential pressure/flow velocity curve, the overall air permeability (resistance, contaltance, etc.) can be easily calculated.
is obtained. For this reason, the measurer can perform measurements with a small number of measurements.
All the data regarding the ventilation of the left and right nasal cavities and the overall nasal cavity ventilation can be obtained, which reduces the burden on the examinee.

[Brief explanation of drawings]

Figures 1 to 3 are diagrams for explaining various methods of measuring nasal airflow rate, Figure 4 is a diagram for explaining an embodiment of the present invention, and Figure 5 is a functional block diagram of the device of the present invention. , Figure 6 is the fourth
Figure 7 is a flowchart showing the program stored in the ROM shown in Figure 7, Figure 8 is a diagram showing the differential pressure 7-hour curve, Figure 8 is the differential pressure displayed on the cathode ray tube display shown in Figure 4.
It is a figure showing a flow velocity curve. 20... Differential pressure detector 21... Flow rate detector 23... Multiplexer 24... Sample/hold circuit 25... A/D converter 11- 26... Microcomputer 27... eP U 28...ROM 29...R, AM 30...Interface 32...Keyboard 33...CRT display 34...Printer agent Patent attorney Books 1) Takashi 12- Figure 1 Figure 2 Figure 3

Claims (1)

[Claims] a differential pressure data storage means for storing differential pressure data corresponding to the differential pressure between the front and rear nasal cavities of the left and right nasal cavities of the subject, respectively, in correspondence with the time at which the differential pressure was measured; and flow velocity data storage means for storing flow velocity data corresponding to the flow velocity within the area in correspondence with the time at which the flow velocity was measured; interpolation calculation means for interpolating the flow velocity in the left and right nasal cavities at the same predetermined differential pressure for each nasal cavity; and a flow velocity in the left nasal cavity corresponding to the predetermined pressure difference based on the calculation result of the interpolation calculation means. What is claimed is: 1. A data processing device for measuring nasal air permeability, comprising: an adding means for adding the flow velocity in the right nasal cavity; and a data processing means for performing data processing based on the addition result of the adding means.