JP3527302B2 - FV waveform synthesis method for FV waveform analysis - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention belongs to the field of public health. More specifically, the present invention belongs to the field of evaluation of the ventilation function of the lung, and the FV for performing the FV waveform analysis as a reference value.
The present invention relates to a method for synthesizing a V waveform.

[0002]

2. Description of the Related Art In order to objectively evaluate the function of ventilation (including gas exchange) of the lungs, it is necessary to analyze a subject's expiratory maximum flow rate curve (MEFV curve, or simply FV curve). This has been done conventionally. This gives the FV curve 2
The evaluation is performed by applying various indices (parameters) derived from a curve type and a coefficient of a quadratic equation.

[0003] The FV curve is determined by measuring with a spirometer the subject inhales maximally and exhales as fast as possible. However, it is often the case that the subject cannot exhale at a stretch to the maximum exhalation position (exhale all). This occurs if the subject temporarily stops exhaling or coughing midway through exhalation. Also, when the subject is elderly or sick, exhalation may not be continued. In such a case, the descending leg of the FV curve rapidly attenuates (falls) near the end point of the curve, making it impossible to accurately perform FV analysis using the curve. Here, the “descending leg” refers to a region where the FV curve descends from the maximum flow rate (PEFR) until the flow rate becomes zero.

Heretofore, there has been no method of obtaining a complete FV curve other than forcing the subject to perform a series of maximum inspiration and expiration again.

[0005]

SUMMARY OF THE INVENTION The present invention has been made in view of the above-mentioned problems, and is intended to synthesize an FV waveform even when an FV curve is incomplete, and perform FV waveform analysis as a reference value. The aim is to expedite the method of obtaining a suitable waveform.

[0006]

According to the present invention, (a)
A flow volume (FV) curve at the time of maximum exhalation from the maximum inspiration and a flow volume (GV) curve at the time of maximum exhalation from the resting inspiration are obtained based on the subject's expiration data. The FV curve and the GV curve are displayed on two-dimensional coordinates with the air volume as the horizontal axis. (C) The intersection X of the FV curve and the GV curve in the rapid decay region is determined. From the first to the intersection X via the maximum flow rate
Drawing a curved portion, (e) drawing a second curved portion on the GV curve from the intersection X to the maximum exhalation position Y of the GV curve, and (f) connecting the first curved portion and the second curved portion,
A method for synthesizing an FV waveform for FV waveform analysis, comprising the steps (a) to (f), is provided. In the present invention, preferably, step (d),
(E) and (f) are performed on two-dimensional coordinates different from the two-dimensional coordinates in step (b).

[0007]

In the present specification, "FV waveform analysis" means (1) finding a dV / dF index based on an FV waveform, and (2) FV waveform.
(3) If the approximation of the quadratic expression is not sufficient, the curve is approximated to a polynomial expression.

The synthesized FV curve synthesized according to the present invention is not an actually measured curve (actually measured value), and is used as a reference value to complement conventional FV waveform analysis and the like.
It should be understood that the meaning of the present invention as "a reference value based on the V curve and its analysis".

According to the present invention, first, the subject's exhalation F
A V curve is obtained and displayed on two-dimensional coordinates. During breath measurement,
FIG. 4 schematically shows an FV curve in which expiration is caught for some reason such as coughing or shortness of breath. FIG. 5 is an actual measurement example in such a case. In both figures, FV is a flow rate curve when the maximum exhalation is performed from the maximum inspiration, and GV is a flow rate flow rate curve when the maximum exhalation is performed from the quiet expiration. As is clear from the figure, the FV curve rapidly attenuates (falls) downstream of the descending leg, that is, near the end point. In FIG. 5, the intersection of the FV curve and the GV curve in this region is represented by X (point 8 in FIG. 4), and the end point of the GV curve, that is, the maximum expiratory position is represented by Y (point 10 in FIG. 4). Since the FV curve is incomplete (missing) in the XY range, it is impossible to perform accurate waveform analysis from this FV curve.

Therefore, when the GV curve in the XY region is partially connected to the FV curve and the waveform (curve) is synthesized, a curve close to a normal FV curve (illustrated in FIG. 3) is completed. Specifically, from the start point (0th position) of the FV curve, the maximum flow rate position (F
Then, an FV curve is drawn (traced) to the intersection X through the apex of the V curve, and a partial GV curve from X to Y is drawn to complete a pseudo FV curve.

According to the present invention, if there is a normal GV curve, even if the FV curve of the subject is incomplete as shown in FIGS. According to the synthesizing method of the present invention, the FV curve is displayed in two-dimensional coordinates on an appropriate display means (screen), and further, the GV curve is displayed on the same screen in a superimposed manner. Waveform (for example, the rising portion of the GV curve or FV
Erase the falling part after the X of the curve) and delete the necessary F
Only the V composite waveform can be displayed.

Further, on a screen different from the display screen of the FV curve and the GV curve, an FV waveform may be synthesized from the FV and GV curve data newly stored in the memory and displayed.

On these screens, the dV / dF index and the like can be calculated and displayed together. FIG. 6 shows an example of the result of performing such a series of FV waveform synthesis.

FIG. 6 also shows a quadratic curve (13) approximated to a quadratic equation as described later. The method of synthesizing an FV waveform according to the present invention can be achieved by an apparatus described in detail in the following embodiments.

[0015]

The present invention will be described more specifically with reference to the following examples.

[0016] 1. Synthesis of FV Waveform FIG. 1 is a block diagram showing an electrical configuration of a spirometer or the like for obtaining an FV curve of a subject's expiration. The subject whose pulmonary function is to be tested is, for example, in a standing position, inhaling as much as possible, holding the nose and holding the tube 21 in the mouth,
The expiration is supplied to the flow meter 22 as soon as possible. The processing circuit 23 realized by a microcomputer or the like includes:
In response to the output of the flow meter 22, the flow rate and the air volume are calculated and stored with the passage of time, and the results are displayed on the visual display means 25 using a cathode ray tube or a liquid crystal display element, and are required. If there is, it is recorded on the recording paper 27.

On the other hand, instead of the data sent from the flow meter 22, the processing circuit 23 reads a flow rate air volume curve drawn in advance on a recording paper 27 by a reading device 28 such as a digitizer and obtains the digitized data. It is also possible to insert. For the flow rate, for example, for each 10 ml of air volume, the time required for the measurement is measured, and the flow rate is calculated.

FIG. 2 is a flowchart for explaining the operation of the processing circuit 23 shown in FIG. Step m
The process proceeds from step 1 to step m2, where the time lapse of the flow rate measured by the flow meter 22 is measured, and in the next step m3, the air volume and the flow rate are stored in the memory 24 in association with each other.
At step m4, the flow rate and air volume are graphed, and step m5
These are recorded on the recording paper 27. In step m6, the series of operations is completed.

FIG. 3 shows the FV obtained as described above.
It is a schematic example of a curve, the flow rate F (l / sec) on the vertical axis,
The volume V (l) is plotted on the horizontal axis. The flow rate rapidly increases in the initial short time, reaches the flow rate maximum value PEFR, and then decreases relatively slowly to the residual expiration point B (RV) at the maximum expiratory position. The range from the maximum flow rate value PEFR to the point B is called a descending leg, and changes as shown by curves 1 to 4 depending on the state of the airway of the subject. For example, the subject who draws the curve 4 is often a nasal allergy patient.

The method of synthesizing the FV waveform for analyzing the FV waveform according to the present invention will be described in detail with reference to another schematic FV curve shown in FIG.

Curve 1 represents an FV curve (here also abbreviated as FV) at the time of maximum exhalation from maximum inspiration, as in FIG. Curve 5 represents the FV curve (here also abbreviated as GV) when the maximum exhalation is performed from the quiet inspiration (normal state). Curve 1
And between the intersections 6 and 7 of the curve 5, the flow rate is GV> FV, and at the intersections 6 and 7, the FV and the GV are almost equal in the flow rate. Point 8 on curve 1 indicates that expiration is interrupted,
Indicates a point where the flow rate drops rapidly. This applies when the subject experiences shortness of breath or coughs. The end point 9 represents the remaining air amount at the maximum expiratory position, and the point 10 is the end point of the GV representing the residual air amount of the resting expiratory position, which is located behind the end point 9 of the FV on the horizontal axis.

Therefore, if for some reason the FV is interrupted as shown in FIG. 4 and does not draw a smooth curve, G
With V, without forcing the subject to exhale again,
V waveform can be synthesized. That is, PEFR position 1 of curve 1
FV is traced from 1 to 7 and from 7 to 8
During the period, trace either FV or GV, and point 8
The GV is traced from to the point 10.

In a series of these operations, FV and GV can be displayed on a chart as shown in FIG. 4 and traced manually, and an ideal composite FV curve can be drawn. It is convenient to store the data for the calculation in the memory 24, calculate them again in the processing circuit 23, and then display the synthesized FV curve on a visual display means 25 such as a screen or a recording paper. It is also conceivable that one curve already drawn on the recording paper is read by the reading device 28 and combined with the data of the other curve in the memory 24 to similarly obtain a combined FV curve.

The advantages of the FV waveform synthesis method according to the present invention include:
If the GV curve from the resting breath is obtained, the composite FV curve can be drawn even if the measurement and the flow rate for obtaining the FV curve from the maximum breathing and the interruption during the measurement fail. F
To get the V-curve, without having to repeat the measurement,
An FV curve can be synthesized from a GV that is easily obtained by the subject from the FV. Therefore, the number of times of the maximum call measurement can be reduced, and the burden on the elderly and the sick is reduced. In addition, it is not always necessary to call up to the end, and a reduction in measurement time can be expected.

FIG. 5 shows an example of the actually measured FV and GV curves. In the figure, X is the intersection with the GV in the fast decay region of the FV, which corresponds to point 8 in FIG. Y represents the end point of the GV, the maximum expiratory position, and corresponds to point 10 in FIG. In this example, FIG.
If you connect GV to FV and X in exactly the same way as
A composite FV curve can be obtained.

Further, based on the synthesized FV curve, dV
By calculating and plotting the (air volume) / dF (flow rate) index,
For example, as shown in FIG. 6, a dV / dF distribution curve 12 is obtained. FIG. 6 shows a dV / dF curve 12, an actually measured FV curve 1,
This represents an approximated quadratic curve 13 (described later). The curve examples displayed in FIGS. 5 and 6 are derived from actual measurement data shown in Tables 1 and 2, respectively.

[0027]

[Table 1]

[0028]

[Table 2]

As described above, by synthesizing and further analyzing the FV waveform, calculating various parameters (for example, dV / dF), evaluating the pulmonary function, and identifying the cause of the dysfunction,
Ultimately, health management including lifestyle is possible. The implementation of the present invention based on this concept will be described below with reference to a few embodiments.

[0030] 2. Approximation of FV Waveform to Quadratic Curve In FIG. 3, curves 1 to 4 indicating descending limbs of the FV curve can be approximated to quadratic curves using the following equation 1.

[0031] In y = a0 + a1 · X + a2 · x 2 ... (1) Equation 1, y is a flow, x is the relative air amount R, a0 is a constant. When the constant term a0 in the equation, the coefficient a1 of the first-order term, and the coefficient a2 of the second-order term are calculated and plotted with a1 as the vertical axis and a2 as the horizontal axis, the result is as shown in FIG. In the figure, lines 14 and 15 are based on the following data (Table 3). Line 16 shows a straight line at the time of bronchial asthma attack.

[0032]

[Table 3]

The calculation for obtaining a1 and a2 is briefly described below with reference to FIG. FIG. 8 is a flowchart for explaining the operation when the processing circuit 23 shown in FIG. 1 is applied to coefficient determination. Move from step n1 to step n2,
The elapsed time of the flow rate measured by the flow meter 22 is measured, and in the next step n3, the air volume and the flow rate are stored in the memory 24 in association with each other. The processing circuit 23 is a memory 24
The peak position of the descending limb of the flow rate airflow curve stored at the time is detected, and the maximum flow rate PEFR at that time and the airflow V1 at that time (see FIG. 3) are obtained. In step n5,
Regarding the air volume of the flow air volume curve, either the relative air volume or the absolute air volume is selected. The relative air volume R is expressed by Expression 2.

R = VCX / VC1 (2) Here, VC1 is a volume from the volume V1 at the peak of the descending leg to the maximum exhalation position (RV position) in FIG. 3, and VC1 = VC−V1. (3) VCX indicates those points A (PEFR position) and B (RV position)
It shows the amount of air going back from the RV position between the two. Therefore, the above-mentioned relative air volume represents the degree of air volume when the air volume VC1 at the peak of the descending leg is set to 1.0 and the RV position is set to zero. By employing such a relative air volume, the descending limb can be evaluated relatively among a large number of subjects. The absolute volume is a volume unique to each subject, and can be evaluated for each subject by performing an operation based on the absolute volume.

After the combination of the relative air volume R and the flow rate corresponding to the relative air volume R is obtained in this way, in step n6, the quadratic equation of the equation 1 is applied from the obtained relative air volume and the flow volume. Do.

At step n7, the value obtained by calculating the coefficient a1 of the first-order term and the coefficient a2 of the second-order term of the quadratic equation applied to the descending leg is adopted. At the next step n8, the value shown in FIG. The coordinate position + (a2, a1) on the display surface to be displayed is displayed. Thus, in step n9, a series of operations ends. When the absolute air volume is selected in step n5, x in Expression 1 becomes the absolute air volume.

The quadratic curve of the subject thus obtained is compared with the actually measured FV curve in FIG. In the figure, a line 13 indicates a calculated quadratic curve, and a curve 1 is an actually measured curve.

Although it is possible to obtain a higher-order regression equation up to the tenth-order equation and apply the regression equation to the descending limb, even if the second-order regression equation is applied, for example, the sixth-order regression equation is applied, Since there is almost no difference, it is preferable in practice to approximate with a simple quadratic expression.

[0039] 3. Calculation of R _AT Next, a coefficient gradient index (R _AT ) is calculated. As described above, the first-order coefficient a1 and the second-order coefficient a2 of Equation 1 are calculated, and a1 is represented on the two-dimensional coordinate axis by the ordinate and a2 is represented by the abscissa, as shown in FIG. A straight line OP connecting the origin O point P (a2, a1)
Is the angle formed by the horizontal axis (a2 axis) with θ, θ = tan ⁻¹ (a1 / a2) (4) θ is expressed in degrees, and a value expressed by the following equation that differs depending on the sign of a1 and a2 is defined as a coefficient gradient index (R _AT ).

R _AT = θ ° / 180 ° (a1> 0, a2> 0: Quadrant I) (5) R _AT = 1 + (θ ° / 180 °) (a1> 0, a2 <0: IIth (Quadrant) (6) R _AT = − (1−θ ° / 180 °) (a1 <0, a2 <0: Quadrant III) (7) R _AT = θ ° / 180 ° (a1 <0, a2) > 0: IV quadrant) (8) The one-second rate FEV _1.0 % (abbreviated as FEV) is the expiration volume for the first second when exhaling as much as possible and exhaling it as expiration as soon as possible. Since it is displayed as a ratio (percentage) to the total expiratory volume (forced vital capacity), it can be obtained by the spirometer described in FIG. Based on the data from the pyrometer, FEV, in accordance 10 the calculation for obtaining the R _AT, outlined below.

[0041] FIG. 10 is a flowchart for explaining the operation of the FEV, processing related to R _AT circuit 23 shown in FIG. Starting at step p1, the clock in the processing circuit 23 starts, and at the same time, a signal is sent from the flow meter 22 every 10 ml of exhalation. In step p2, the flow rate for each 10 ml is calculated from the air volume and the time, and step p3
To store the air volume and flow rate in the memory 24. Step p4
It is determined whether or not one second has elapsed, and if one second has elapsed, the air volume up to that time is calculated as one second in step p5, and stored in the memory 24 in step p6. In step p9, it is determined whether the flow rate has become 0, and if the flow rate has become 0, it is determined that the volume has reached the maximum expiratory position, and in step p10, the total expiratory volume (forced vital capacity) is calculated. Are stored in the memory 24 at step p11. If the flow rate does not become 0 at step p9, steps p7 and p8 are repeated until the flow rate becomes 0. In step p12, an FV curve is obtained from the flow rate and the air volume stored in the memory 24, and this is recorded on the recording paper 27 in step p13. In step p14, the FV curve is approximated by a quadratic curve,
Obtains the coefficients of a first order term and a second order term, further obtains the R _AT, stores it in the memory 24 at step p15. The FEV is obtained from the one-second amount and the forced vital capacity stored in step p16. In step p17, this FEV and R _AT
Are graphed, and are recorded on the recording paper 27 at step p18. At step p19, a series of operations ends.
Note that the visual display unit 25, and 2 minutes screen, FV curve one is, the other to see a graph of the relationship between FEV and R _AT, the change-over switch, also enlarge either it can.

[0042] 4. FEV and correlation thus determined was FEV and vertical and R _AT with R _AT, those displayed on the horizontal axis, a diagram 11. In this figure, since the predicted vital capacity VC _P is used instead of the forced vital capacity as the FEV, it is represented as FEV (VC _P ). Here, the predicted vital capacity is different from the actually measured vital capacity, and is the vital capacity predicted from the age and height of the subject. In FIG. 11, a line 17 represents a non-smoker and a healthy subject, and lines 18 and 19 represent a non-smoker and a subject who is likely to cause airflow obstruction.
In particular, the line 18 is of a type that is likely to cause obstruction mainly in the upper airway. In general, each line tends to worsen airway obstructive lesions as it goes from lower left to lower left. Further, the curve SA corresponds to a case where a healthy person (that is, a person who is unlikely to cause airway changes) smokes, and the curve SB corresponds to a case where a person who is likely to cause airway obstruction smokes.

The area below the second inlaid eye (lower left in FIG. 11) is in a state where the lesion has progressed, and the patient is hospitalized and needs treatment.

[0044] R _AT and FEV represented in FIG. 11 (VC _p)
Table 4 shows an example of the data used to plot the relationship of
Shown in

[0045]

[Table 4]

On the vertical axis, FEV (VC _p ) is used instead of FEV (VC _p ).
EV (g) (forced vital capacity) or FEV
When (t) (inspired vital capacity) is adopted, both figures are shown in FIG.
become that way. In the figure, lines 20, 21, and 22 correspond to lines 17, 18, 19, respectively, in FIG. Thus, line 20 represents a non-smoker and healthy subject. An example of data used to plot the relationship between R _AT and FEV (g) or FEV (t) represented in Figure 12 are shown in Table 5.

[0047]

[Table 5]

In FIG. 10, the FEV is set as one second.
(G), FEV (t) , all calculated to FEV (VCp), if stored in the memory in step l6, optionally each FEV, obtain a R _AT graph. For example, by pressing a function key, FEV (g) → F
It can be set to cycle from EV (t) to FEV (VCp). Therefore, the desired 1 second rate (FEV) and R _AT
Can be displayed in a graph, and detailed evaluation and analysis are possible.

[0049] 5. FEV for lifestyle management in accordance with the evaluation the present invention of ventilation capacity, R _AT
The use of the correlation of will be further described.

As described above, according to the configuration of the present invention, F
To EV (e.g. FEV (g)) and graphically displays the relationship again with R _AT. See FIG. As such, it is useful for the evaluation of air-conducting obstructiveness and airway hyperresponsiveness, as described above, and enables the management of lesions in subjects.

[0051] In addition, based on the FEV and R _AT,
Zone. Upper right area of line 20 and R _AT ≧ 0.2
The zone composed of the above is defined as zone A. Subjects in this zone are in good health. FEV80 above, R _AT
A portion excluding the zone A among the zones of ≧ 0 is defined as a zone B. Subjects in this zone should change their lifestyle. A zone where the zone of FAT 70 or more and 80 or less and R _AT ≧ 0 is combined with the zone of FEV 70 or more and R _AT ≦ 0 is defined as zone C. Subjects in this zone need to be screened for disease. FEV5
5 to 70 the following zones defined as zone D _1. Subjects in this zone require disease management. FEV40
Zones of 55 or less and zones of FEV 40 or less are defined as zones D ₂ and D ₃ , respectively. Subjects in this zone require hospitalization, hospital visits, and may require emergency treatment. In this way, ventilation performance evaluation including lifestyle management can be performed.

6 Comprehensive Evaluation of Ventilation Ability and Gas Exchange Function Next, a comprehensive evaluation of ventilation ability and gas exchange function (also referred to as ability) for health management by lifestyle management according to the present invention will be described.

[0053] Although the above embodiments are those aimed at lifestyle management from the relationship between the R _AT and FEV (ventilation capacity), it gas exchange capacity _{(P 'co, D' LCO} , D '
_{LCO / V 'A, P'} co (22), D 'Lco (22), D' LCO / V '
_{When A (22)} , SPO ₂ ) is added as a parameter and three-dimensionally evaluated, the respiratory function test index and the health management are more logically related.

FIG. 14 shows the values obtained by _calculating the CO lung diffusion capacity D ' _LCO or D _LCO as an index of the gas exchange function of the lung and _VA ' from the dilution of the alveolar volume _VA or He at that time. It is a figure for explaining a technique for calculating and calculating D ' _LCO / _VA ' or D _LCO / _VA .

As a method for measuring the CO lung diffusion capacity D ' _LCO or D _LCO, a single breath method is adopted, which is also called a breath holding method. The subject inhales the mixed gas at a stroke from the maximum expiratory position RV to the maximum inspiratory position TLC, and stops breathing at this position for exactly 10 seconds from the start of inhalation. Thereafter, the maximum expiration is rapidly performed, the first 750 mL is discarded, and the remaining exhaled gas is collected in the sample bag 39 (see FIG. 15) to perform gas analysis. The mixed gas is 0.3% CO, 10%
He, a four-component gas mixture of 20% O ₂ and 70% N ₂ .

F _ACO decreases with time because CO is taken in the lungs, but does not change with time because He is not taken in the lungs. If the calling He concentration is F _AHe , t = 0
F _ACO (0) in is obtained as _{F ACO (0) = F ICO} · F AHe / F IHe ... (9). "Is a _{CO / P ACO ... (10)} .V" defined from the D _LCO = V _CO is the first derivative of V _CO. This equation _{V "CO = -dV CO (t} ) / dt P ACO = P ACO (t) ... (11) Substituting _{dV CO (t) / dt =} -D LCO · P ACO (t) ... (12 Here, V _CO (t) = F _ACO (t) · V _A (t) (13) Since d V _CO (t) / dt = F _ACO (t) · dV _A (t ) / Dt + V _A (t) · dF _ACO (t) / dt (14), and if _VA (t) = constant (15), then dV _A (t) / dt = 0 (16) Because there is, dV _CO (t) / dt = _VA · dF _ACO (t) / dt (17) and P _ACO (t) = (P _B -47) F _ACO (t) (18) Substituting into the above equation

[0057]

(Equation 1)

This is Krogh's equation. If t is seconds,

[0059]

(Equation 2)

By substituting the above equation 9 into FACO (0),

[0061]

[Equation 3]

[0062] Unit of V _A is MlSTPD, as t = 10 seconds, can be determined by calculating the ^{_{D LCO (ml · min -1 ·}} torr -1).

D _LCO is calculated by equation 21, and there are two ways to determine _VA . The first Determination, in addition residual capacity measured in advance in D intake air amount at the time of _LCO measurement (V _I) to (RV), determined amount of alveolar the (V _A). Normally RV to TL
Since inhalation of up to C position V _I is the intake vital capacity, V _A is almost equal to total lung capacity (TLC). The second way is
There is a method of measuring _VA by the following equation from the dilution of He at the time of measuring D _LCO . In this case, to distinguish it from normal _VA ,
It is generally represented by _VA '.

[0064] relationship of _{F IHe (V I -V D)} = F AHe · V A '... (22) is satisfied. From this, the _{V A '= F IHe (V} I -V D) / F AHe ... (23). In this case, since V _D is extremely small compared to V _I , it is possible to set V _I -V _D ≒ V _I (24).

[0065] determine the 'V _A in _{= V I · F IHe / F} AHe ... (25)' V A. V as _LCO 'where D were substituted for V _A of formula 21' to distinguish it from the conventional D _LCO.

CO partial pressure _P'CO and P '
_{co (22)} is expressed by the following equations 26 and 27.

[0067]

(Equation 4)

P ′ _{CO (22)} = (P ′ _co / BMI) × 22 (27) In the above formula, BMI is an abbreviation of “Body Mass Index” and represents the degree of obesity, and the weight (kg) / height (m) ² Is an index calculated by

Therefore, P'co ₍₂₂₎ is also referred to as standard weight-normalized P'co.

Similarly, D ' _LCO and D' _LCO / V _A are given by the following equation (2).
According to 8, 29, standard weight can be standardized.

D ′ _{LCO (22)} = (D ′ _LCO / BMI) × 22 (28) D ′ _LCO / V ′ _{A (22)} = (D ′ _LCO / V ′ _A / BMI) × 22 (29) ) D ' _{LCO (22)} and D' _LCO / V ' _{A (22)} are also referred to as standard weight standardized D' _{LCO (22)} and D ' _LCO / V' _{A (22)} , respectively.

Equation 26 represents the transition of the gas exchange state in the alveoli, which is the partial pressure difference of carbon monoxide per unit time, and the unit is mTorr / sec. The first term of equation 26 (0.30
/ _FICO ) reduces the concentration of carbon monoxide in the intake gas by 0.30.
(%). The second term (P _B -47) is
Pressure of total dry gas in the lungs. The first half of the third term $ F
_ICO × F _AHe / F _{IHe あ り} is the concentration of carbon monoxide in the lung at the initial _stage (t = 0), and F _ACO is the concentration of carbon monoxide in the lung at the end _stage . (P _B -47)
Multiplied by the partial pressure of carbon monoxide in the early and late lungs. The numerator 10 in the fourth term changes the pressure from Torr to mT
It is multiplied by 1000 to make it orr (millitorr), and the gas concentration is expressed in%, so it is divided by 100, that is, 1000/100 = 10.

As described above, Equation 27 is the partial pressure difference of carbon monoxide per unit time standardized to the standard body weight, and the unit is mT.
ORR / sec.

The first term of equation 27 is P 'per unit BMI.
It has the advantage that it can be compared with others by correcting height (m) and weight (kg) with co.

FIG. 15 is an overall system diagram of one embodiment of the present invention. The subject puts a tube 21 in his mouth to make a simultaneous, and thus identical, measurement of the subject's ventilation capacity and gas exchange function. The mixed gas source 40 supplies the mixed gas to the first switching valve 41. First
A flow meter 22 for measuring the flow rate of expiration is connected to the switching valve 41, and the output of the flow meter 22 is supplied to a processing circuit 23, and the flow rate and the air volume are sampled and read over time. Expiration from the flow meter 22 is guided from the pipe line 42 to a second switching valve 43, and the second switching valve 43
Exhaled air from line 42 is vented to atmosphere from line 44 or directed to flexible sampling bag 39 via line 45. The CO concentration of the breath in the bag 39 is detected by the CO concentration detecting means 46, and the He concentration is detected by the He concentration detecting means 47. The outputs of the respective concentration detecting means 46 and 47 are supplied to the processing circuit 23. Can be

FIG. 16 shows the processing circuit 23 shown in FIG.
3 is a flowchart for explaining the operation of FIG. The process proceeds from step o1 to step o2, in which the first switching valve 41 is switched from the first position 41a to the second position 41b, and the subject holds the pipe 21 to the mouth while discharging the mixed gas from the mixed gas source 40 to the maximum expiratory position RV. To the maximum inhalation position TLC at once, and at this position, stop breathing for exactly 10 seconds from the start of inspiration. Next, in step o3, the first switching valve 41 is switched to the first position 41a, and at this time, the second switching valve 43 is set to the first position 43a, and the maximum switching is rapidly performed. At this time, in step o 4, the passage of the expiration flow by the flow meter 22 is measured and stored in the memory 24. In step o5, 750 mL is measured from the beginning of exhalation, and the exhalation of 750 mL is measured by the second switching valve 43.
From the first position 43a through the conduit 44.
In the next step o6, the second switching valve 43 is moved to the second position 4
3b, and in step o7, 1000 mL of the remaining exhaled gas is stored in the bag 39 via the pipe line 45. At that time, also in step o8, the measurement value of the flow meter 22 is measured with time. It is stored in the memory 24. In step o9, 10 in step o7
After the measurement of 00 mL, the position is switched to the first position 43a to disperse the remaining exhaled air to the atmosphere. At this time, the measured value of the flow meter 22 is also stored in the memory 24 from the processing circuit 23. Thus, the air volume and the flow rate are stored in the memory 24 in association with each other.

The processing circuit 23 is provided with a visual display means 25 using a cathode ray tube or a liquid crystal display element, and its display surface 26 can display the above-mentioned display drawings and the like. When the flow rate curve already measured is drawn on the recording paper 27, the recording paper 27 is supplied to a reading unit 28 that optically reads the recording paper 27, and the flow rate air volume recorded on the recording paper 27 is supplied. It is also possible to read the quantity curve and store it in the memory 24.

The processing circuit 23 detects the peak position of the descending leg of the flow rate curve stored in the memory 24 at step o10, and obtains the maximum flow rate PEFR at that time and the flow rate V1 at that time. At step o11, either the relative air volume or the absolute air volume is selected for the air volume of the flow air volume curve.

After the combination of the relative air volume R and the flow rate corresponding to the relative air volume R is obtained in this way, in step o12, a quadratic equation is applied from the obtained relative air volume and the flow volume.

[0080] In step O13, adopts the value of the calculation result of the coefficient of the first-order coefficients a1 and quadratic terms of quadratic, which is fitted to the lower limb a2, obtaining coefficients gradient index R _AT. According to the next step o14, the one second rate FEV is calculated. When the absolute air volume is selected in step o11, the quadratic variable x becomes the absolute air volume.

In step o15, D ' _LCO , D' _LCO /
_{V 'A, D' LCO (} 22), D 'LCO / V' A (22), P 'CO,
Calculation of parameters such as P ' _CO (22)
At 16, a three-dimensional display as shown in FIG. 17 is performed.
In this way, by measuring the time-series ventilation capacity and gas exchange function using the steps of FIG. 16, a three-dimensional display can be performed as shown in FIG. Such three-dimensional display shown in FIG. 17 is achieved by the display means 25.

The measured SPO ₂ is input at step o15, and this value can also be displayed three-dimensionally at step o16.

[0083] Similar to the display of _{FEV-R AT P 'CO,} P'
co ₍₂₂₎ , SPO ₂ , D ' _LCO , D' _{LCO (22)} , D ' _LCO /
If V ' _A and D' _LCO / V ' _{A (22)} are stored in the memory at step o15, a three-dimensional display graph having each of them as the Z axis can be obtained. For example, by pressing a function key, P ' _CO → P' _{CO (22)} → D '
_LCO → D ' _{LCO (22)} → D' _LCO / V _A → D ' _LCO / V' _{A (22)}
→ SPO ₂ and set to cycle.

According to a preferred embodiment of the present invention, FIG.
6 in step o16 displayed first 2-dimensional FEV and R _AT before displaying the various parameters 3D, identifying zones belongs subject as described above. Depending on the zone, _P'CO , P 'as Z-axis parameters for 3D display
_{CO (22)} , D ' _LCO , D' _{LCO (22)} , D ' _LCO / V' _A , D '
_{LCO / V 'A (22)} , to select the most optimal gas exchange capability index from the group of SPO _2, to implement the three-dimensional display in step o16.

Therefore, in step o15, only a specific parameter can be calculated from the result of the two-dimensional display. After calculating all the parameters, the parameter is stored in the memory 24, and the desired Z-axis parameter is calculated. A configuration is possible in which only the three-dimensional display is completed by taking out only the three-dimensional display. In any case, a desired Z-axis parameter (gas exchange capacity) can be selected depending on the health group to which the subject belongs. Thus, comprehensive lifestyle management becomes possible.

Although the apparatus or method of the present invention has been described with reference to the embodiments, the scope of the present invention is not limited to the disclosed specific examples.

[0087]

As described above, according to the present invention, since the waveform of the FV curve can be complemented by the GV curve, it is necessary to analyze the FV waveform even if the data of the subject is not complete enough to draw a normal FV curve. An FV waveform is obtained. The number of times of the maximum call measurement may be about 1 to 2 times, and the subject is not forced to perform frequent measurements, so that the burden on the sick, elderly, and the like is reduced. In addition, even a healthy person can evaluate even when the maximum exhalation has not been performed until the end after the maximum inhalation, so that the measurement time can be expected to be shortened, which leads to an improvement in the examination ability. The analysis of the FV waveform is useful for evaluating the ventilation function of the lungs, assisting diagnosis of lung disease, and the like. The analysis of the FV waveform by synthesizing the FV waveform is a reference value, but has a very important meaning in health care and public health. .

[Brief description of the drawings]

FIG. 1 is a block diagram showing an electrical configuration of a device for obtaining an FV curve.

FIG. 2 is a flowchart when the processing circuit 23 shown in FIG. 1 is operated to display an FV curve.

FIG. 3 is a view schematically showing an FV curve of a subject's expiration.

FIG. 4 is a schematic diagram for synthesizing an FV curve according to the present invention.

FIG. 5 is a diagram showing an example of both FV and GV curves.

FIG. 6 is a diagram showing an example of analyzing and synthesizing an FV waveform according to the present invention.

FIG. 7 is a coefficient correlation diagram (a1,
It is a figure which shows a2).

FIG. 8 activates the processing circuit 23 according to the invention,
It is a flowchart at the time of calculating and displaying 1 and a2.

FIG. 9 shows coefficients a1 and 2 of a first-order term of a quadratic curve according to the present invention.
It is a graph showing a relationship between the coefficient a2 and the coefficient gradient index R _AT of the next section.

FIG. 10 operates the processing circuit 23 according to the present invention;
Calculating a 1, a2, R _AT, is a flowchart when displaying.

[11] accordance connexion to the present invention, the FEV (VCp) R _AT T
FIG. 6 is a diagram displaying an example showing the relationship of FIG.

FIG. 12 shows FEV (g) or FEV according to the invention
It is the figure which displayed an example showing the relation between (t) and _RAT .

According [13] The present invention is a diagram displaying the correlation diagram in the zone of FEV / (g) and R _AT.

FIG. 14 is a schematic diagram illustrating a tidal breathing method according to the present invention.

FIG. 15 is a system diagram showing the overall configuration of the apparatus according to one embodiment of the present invention.

FIG. 16 operates the processing circuit 23 according to the present invention;
R _AT , FEV, D ' _LCO / V' _A , P ' _CO , P' _{CO (22)} ,
D ′ _LCO , D ′ _{LCO (22)} , D ′ _LCO / V ′ _{A (22)} are calculated,
It is a flowchart when displaying additional 3 dimensional enter the SPO _2.

FIG. 17 is a diagram showing a three-dimensional display of ventilation capacity and gas exchange function according to the present invention.

[Explanation of symbols]

21 tubes 22 Flow system 23 Processing circuit 24 memory 25 Display means 26 Display surface 27 Recording paper 28 Reader 40 mixed gas source 41 1st switching means 43 Second switching means 46 CO concentration detection means 47 He concentration detection means

Continuation of the front page (56) References JP-B-51-33675 (JP, B2) JP-B-53-42999 (JP, B2) JP-B-58-25453 (JP, B2) JP-B-1-13371 (JP , B2) Tables Hei 5-505969 (JP, A) Patent 2786807 (JP, B2) Patent 3264536 (JP, B2) (58) Fields investigated (Int. Cl. ⁷ , DB name) A61B 5/08 G06F 17 / 60 JICST file (JOIS)

Claims (2)

(57) [Claims] 1. (a) A flow volume (FV) curve at the time of maximum exhalation from maximum inspiration based on the subject's expiration data and a flow volume (GV) at the time of maximum exhalation from resting inspiration
(B) FV curve and GV curve are displayed on two-dimensional coordinates with the flow rate as the ordinate and the air volume as the abscissa, and (c) the intersection X of the FV curve with the GV curve in the rapid decay region. (D) Draw a first curve portion from the maximum intake position of the FV curve to the intersection X via the maximum flow amount, and (e) On the GV curve, the maximum exhalation position Y of the GV curve from the intersection X FV waveform for FV waveform analysis, comprising the steps of (a) to (f), wherein the second curve portion is drawn and (f) connects the first curve portion and the second curve portion. Synthesis method. 2. Steps (d), (e), and (f)
2. The method according to claim 1, wherein the step (b) is performed on a two-dimensional coordinate different from the two-dimensional coordinate in step (b).