JP2000300526A - Manometer - Google Patents

Abstract

PROBLEM TO BE SOLVED: To achieve the optimal determination of a blood pressure corresponding to data. SOLUTION: A manometer has an arterial pulse wave-extracting part 101 to extract a dynamic pressure from an output value of an A/D converter 16, and a cuff pressure-extracting part 102 to extract a static pressure, a memory part 103 to store the dynamic and static pressures, an arithmetic part 104 to performs a computation using the dynamic and static pressures and a blood pressure determination part 105 to determine a blood pressure utilizing the results of the computation. The manometer is provided further with a memory part 110 to store a pulse wave extracted by the arterial pulse wave extracting part 101, a pulse wave-subdividing computation part 111 which adds a plurality of pulse waves, for instance, to subdivide, an arithmetic part 112 to compare the subdivided pulse wave with a specified pulse wave, a stratification part 113 which quantifies the results of the comparison to stratify a data obtained from the A/D converter 16 into a plurality of stratums based on the results of the quantification and a stratification computing determining part 114 to alter a formula for determining the blood pressure in stratums obtained by the stratification.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention relates to a sphygmomanometer for measuring a blood pressure by extracting a pulse wave.

[0002]

2. Description of the Related Art FIG. 50 is a block diagram of a conventional sphygmomanometer. The sphygmomanometer shown in FIG. 50 has a cuff 11 as a sensor, a pressure sensor 12 for detecting the internal pressure of the cuff 11, and a pressure sensor for measuring the blood pressure. A pressure pump 13 for feeding air for compressing the part into the cuff 11, a gradual exhaust unit 14 for gradually reducing the internal pressure of the cuff 11 during the measurement, and a large inside of the cuff 11 when the measurement is completed and when the measurement is not performed. A quick exhaust unit 15 that opens to atmospheric pressure, an A / D converter 16 that converts a signal from the pressure sensor 12 into a digital signal, an operation input unit 17 for various operation inputs, and an output unit including a buzzer (not shown) and the like. 1
8, a display 19 for displaying predetermined information, and an A / D converter 1 according to an operation input performed on the operation input device 17.
6 performs various arithmetic processing using the digital signal converted by the pressure pump 13 and the gradual exhaust unit 1.
4A and a computing unit 10PA for controlling the rapid exhaust unit 15 and controlling the output unit 18 and the display unit 19 for output.
And a power supply device 2 for supplying power to necessary parts of the blood pressure monitor
0.

FIG. 51 is a diagram showing the internal configuration of the arithmetic unit shown in FIG. 50, and the arithmetic unit 10PA includes an A / D converter 1
6, an arterial pulse wave extracting unit 101p for extracting a dynamic pressure corresponding to an arterial pulse wave, a cuff pressure extracting unit 102 for extracting a static pressure corresponding to a cuff pressure, and the arterial pulse wave A storage unit 10 that stores the dynamic pressure and the static pressure extracted by the extraction unit 101p and the cuff pressure extraction unit 102 as biological information.
3, a calculation unit 104 that performs calculation using the biological information stored in the storage unit 103, and a blood pressure determination using the calculation result by the calculation unit 104. The determination result is displayed on the display unit 19. A blood pressure determination unit 105p to be displayed is provided. The computing unit 10PA includes an exhaust speed pulse rate monitor 106, a cuff pressure monitor 107, and a cuff pressure control section 108 for calculating a pulse rate and the like using the computation result of the computation section 104.

FIG. 52 is an explanatory diagram of the processing performed by the arithmetic unit 10PA. When the cuff pressure as shown in FIG. 52A from the pressure sensor 12 is converted into a digital signal by the A / D converter 16, the dynamic pressure as a pulse wave as shown in FIG. Is extracted. Thereafter, the magnitude of the extracted pulse wave is quantified, and a pulse wave value as shown in FIG. 52 (c) is calculated. Further, as shown in FIG. 52 (d), the value of the static pressure portion of the cuff pressure is associated with the pulse wave value.

[0005] Then, as shown in Fig. 52 (c), the maximum value max of the pulse wave value is obtained. After this, the maximum value max
From the constant rates S and D%, 2 of max × S and max × D
Points are derived, and the static pressure portions corresponding to these two points are determined as systolic blood pressure and diastolic blood pressure, respectively.

[0006]

In the conventional sphygmomanometer described above, the pulse wave is quantitatively evaluated as a pulse wave value. However, even if the shape of the pulse wave differs depending on the data or the data of the same person, The shape of the pulse wave may vary depending on the time. This appears as an error in the method of determining blood pressure by calculation using a pulse wave value and a constant rate.

The present invention has been made in view of the above circumstances, and an object of the present invention is to provide a sphygmomanometer capable of determining an optimal blood pressure in accordance with data.

[0008]

Means for Solving the Problems In order to solve the above-mentioned problems, the invention according to claim 1 is a means for performing A / D conversion, and means for extracting biological information from the value after A / D conversion by this means. Means for storing the biological information extracted by the means, means for performing an operation using the biological information stored in the means, and means for determining blood pressure using the result of the operation by the means. A sphygmomanometer comprising: means for extracting a pulse wave during measurement, means for adding a plurality of pulse waves extracted by this means, means for subdividing the pulse wave after addition by this means, Means for comparing a pulse wave segmented by this means with a predetermined pulse wave, means for quantifying the comparison result by this means, and the A / D conversion based on the result of quantification by this means A means to stratify the data obtained from the means into multiple layers When it is provided with a means for changing the calculation formula for determining the blood pressure in stratified by each layer in this way.

According to a second aspect of the present invention, there is provided a means for performing A / D conversion, a means for extracting biometric information from a value after A / D conversion by this means, and storing the biometric information extracted by this means. Means, a blood pressure monitor including means for performing calculations using biological information stored in the means, and means for determining blood pressure using the calculation results by the means,
Means for extracting a pulse wave during measurement, means for adding a plurality of pulse waves extracted by this means, means for subdividing and adding the extracted pulse wave, and addition by subdividing with this means Means for comparing the obtained pulse wave with a predetermined pulse wave, means for quantifying the comparison result by this means, and data obtained from the means for performing the A / D conversion based on the result of quantification by this means. To a plurality of layers, and means for changing the calculation formula for determining blood pressure in each layer stratified by this means.

According to a third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in order to extract a pulse wave, an evacuation or pressurizing operation is temporarily stopped when a pulse wave appears, and an operation of maintaining a pressure is performed. In this way, a pulse wave is cut out using the pulse wave start point as a reference point.

According to a fourth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in order to extract a pulse wave, the exhaust or pressurizing operation speed is reduced when a pulse wave appears, and the pressure is reduced or increased. , The pulse wave is cut out with the pulse wave start point as a reference point.

According to a fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, at the time of extraction of the pulse wave, the start point of the pulse wave and the start point of the next pulse wave are determined as the baseline for extracting the pulse wave. And extract the pulse wave.

According to a sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, a straight line determined from pressure change information before the entire pulse is used as a baseline for extracting a pulse wave when extracting a pulse wave. This is to cut out the pulse wave.

According to a seventh aspect of the present invention, in the sphygmomanometer according to the first or second aspect, a straight line obtained as a horizontal line in the time axis direction from the start point of the next pulse wave as a base line for extracting a pulse wave when extracting a pulse wave. By doing so, a pulse wave is cut out.

According to an eighth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the static pressure information included in the pressure pulse wave information at the time of extracting the pulse wave is removed by a high-pass filter, and the pulse wave component is removed. Only the dynamic pressure portion is extracted, and a pulse wave is cut out using the zero point as a reference point.

According to a ninth aspect of the present invention, in the sphygmomanometer according to the eighth aspect, the cutoff frequency of the high-pass filter is one.
Hz or less.

According to a tenth aspect of the present invention, in the sphygmomanometer according to the eighth aspect, the high-pass filter has a Chebyshev-type blocking characteristic.

According to an eleventh aspect of the present invention, in the sphygmomanometer according to the eighth aspect, microcomputer processing can be performed by digitizing the function of the high-pass filter.

According to a twelfth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in the pulse wave extraction, the number of data to be extracted is limited to a predetermined number in order to add a memory limitation.

The invention according to claim 13 is the above-mentioned claim 12.
In the sphygmomanometer described above, a plurality of pulse waves are taken out from the start of measurement and are calculated from time axis information as a pulse wave width of the several pulse waves, as a predetermined number of determination means.

The invention according to claim 14 is the invention according to claim 13.
In the sphygmomanometer described above, a predetermined number is determined based on an average value of time axis information of several pulse waves as a calculating means.

According to a fifteenth aspect of the present invention, the above-mentioned thirteenth aspect is provided.
In the sphygmomanometer described above, a predetermined number is determined based on a median value of time axis information of several pulse waves as a calculating means.

[0023] The invention of claim 16 provides the above-mentioned claim 14.
Alternatively, in the sphygmomanometer according to 15, the increment is given in consideration of the average value and the rate of increase of the median value.

According to a seventeenth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the present pressure change information is estimated from past pressure change information other than the start point of the pulse wave, and the estimated pressure change information is obtained. It is determined by a pulse wave cut off by a straight line or a curve.

[0025] The invention of claim 18 provides the above-mentioned claim 12.
In the sphygmomanometer according to any one of (1) to (16), a predetermined number of pulse waves are extracted from the vicinity of the maximum pulse wave.

According to the nineteenth aspect of the present invention,
In the sphygmomanometer according to any one of (1) to (16), several pulse waves are extracted from the vicinity of the start pulse wave, the vicinity of the end pulse wave, and the vicinity of the maximum pulse wave point, and a predetermined number is determined.

The twentieth aspect of the present invention provides the twelfth aspect.
In the sphygmomanometer described above, a predetermined number is provisionally determined in advance, and a means is provided for invalidating the data if a predetermined threshold value of the portion is obtained by comparison with a portion of the added pulse wave.

According to a twenty-first aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the required memory capacity is reduced by subtracting the obtained sampling data for the added pulse and the subdivided pulse for comparison for a predetermined time. Means.

According to a twenty-second aspect of the present invention, in the sphygmomanometer according to the first or second aspect, all the extracted pulse waves are added to be added and subdivided.

According to a twenty-third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, only pulse waves having a magnitude equal to or larger than a predetermined threshold value are added and segmented.

According to a twenty-fourth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, several pulse waves are taken out near the maximum value of the pulse wave, and are added and segmented.

According to a twenty-fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, several pulse waves are taken out in the vicinity of the systolic blood pressure and the diastolic blood pressure value, and are subjected to addition and segmentation. .

According to a twenty-sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, a pulse wave peak value is set as a criterion for determining whether a pulse wave is valid or invalid.

[0034] The invention of claim 27 provides the above-mentioned claim 26.
In the sphygmomanometer described above, the peak value is defined by a value using the pulse wave start point as a reference point.

The invention according to claim 28 is the invention according to claim 26.
In the described sphygmomanometer, the peak value is defined by a value using the next pulse wave start point as a reference point.

According to the twenty-ninth aspect, the twenty-sixth aspect is provided.
In the sphygmomanometer described above, the peak value is defined by a value using a baseline determined by the pulse wave start point and the next pulse wave start point as a reference line.

According to a thirtieth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, as a criterion for determining whether the pulse wave is valid or invalid, the sphygmomanometer is set based on time axis information as a pulse wave width.

The invention according to claim 31 is the invention according to claim 30.
In the sphygmomanometer described above, the width of the pulse wave is defined by a partial width cut by a reference line parallel to the time axis determined at the start point of the pulse wave.

The invention according to claim 32 is the invention according to claim 30.
In the sphygmomanometer described above, the width of the pulse wave is defined by the partial width cut off by the reference line determined by the start point of the pulse wave and the start point of the next pulse wave.

According to a thirty-third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the addition data of the quantized sampling value is set as the area value of the pulse wave as a criterion for determining whether the pulse wave is valid or invalid. It is.

The invention according to claim 34 is the above-mentioned claim 33.
In the described sphygmomanometer, the area value is defined by a partial area cut by a base line parallel to the time axis determined at the start point of the pulse wave.

The invention according to claim 35 is the invention according to claim 33.
In the sphygmomanometer described above, the area value is defined by a partial area cut by a baseline determined by a start point of a pulse wave and a start point of a next pulse wave.

The invention according to claim 36 is the invention according to claim 33.
In the sphygmomanometer described above, the area value is defined by a partial area cut by a base line parallel to the time axis determined at the start point of the next pulse wave.

The invention according to claim 36 is the above-described claim 2.
In the sphygmomanometer according to any one of 6, 30, and 33, when the pulse wave is invalidated as a result of the invalidity determination, the invalid pulse wave data is deleted.

The invention according to claim 38 is the second invention.
In the sphygmomanometer according to any one of 6, 30, and 33, when the pulse wave becomes invalid as a result of the pulse wave invalidity determination, the invalid pulse wave is combined with the front pulse wave data as a part of the front pulse wave. Things.

The thirty-ninth aspect of the present invention provides the above-mentioned thirty-fifth aspect.
In the described sphygmomanometer, the sampling data after the baseline correction takes an absolute value and does not consider the sign.

The invention according to claim 40 is the invention according to claim 35.
In the sphygmomanometer described above, when the sampling data becomes a negative number after the baseline correction, a process of adding the data as a zero value is performed.

According to a forty-first aspect of the present invention, in the sphygmomanometer according to the first aspect, a portion cut off by one straight line perpendicular to the time axis is defined as the segmented pulse wave.

The invention according to claim 42 is the invention according to claim 41.
In the sphygmomanometer described above, the cut-out area includes a portion after the portion showing the maximum wave height.

The invention of claim 43 provides the above-mentioned claim 41.
In the described sphygmomanometer, a portion cut by a plurality of straight lines perpendicular to a time axis is shown as a definition of a segmented pulse wave.

The invention according to claim 44 is the invention according to claim 43.
In the sphygmomanometer described above, the cut-out area includes a portion after the portion showing the maximum wave height.

According to a forty-fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, as a comparison target, the entire pulse wave is compared with the segmented pulse wave.

According to a forty-sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the segmented pulse wave and the segmented pulse wave are compared as comparison targets.

The invention according to claim 47 is the invention according to claim 45.
Alternatively, in the sphygmomanometer according to Item 46, the comparison is performed with the ratio of the area values.

The invention according to claim 48 is the invention according to claim 45.
Alternatively, in the sphygmomanometer according to Item 46, the comparison is performed by using the ratio of the peak values of one part of the segmented pulse wave and the whole pulse wave.

According to a forty-ninth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, stratification is performed based on a result of the comparison, and a blood pressure determination condition is changed for each stratified layer to determine a blood pressure. is there.

According to the fiftyth aspect of the present invention, there is provided a method as set forth in the forty-ninth aspect
In the described sphygmomanometer, a redundant determination is made in the vicinity of the boundary between the layers using fuzzy inference or the like.

The invention according to claim 51 is the invention according to claim 47.
Alternatively, in the sphygmomanometer according to Item 48, a case where each ratio exceeds a predetermined threshold value is detected.

The invention according to claim 52 is the invention according to claim 51.
In the sphygmomanometer described above, a means for detecting a case where each ratio exceeds a predetermined threshold value and notifying the result is provided.

The invention according to claim 53 is the invention according to claim 47.
49. The sphygmomanometer according to 48, further comprising means for recording a change in each ratio and evaluating the result.

According to a fifty-fourth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, there is provided a function capable of capturing the number of inflection points of the pulse wave.

According to a fifty-fifth aspect of the present invention, in the sphygmomanometer according to the second aspect, a portion cut off by one straight line perpendicular to the time axis is defined as the segmented pulse wave.

According to a fifty-sixth aspect of the present invention, in the sphygmomanometer according to the second aspect, a portion cut out by a plurality of straight lines perpendicular to the time axis is defined as a segmented pulse wave.

[0064]

FIG. 1 is a block diagram of a sphygmomanometer according to an embodiment of the present invention. The embodiment will be described below with reference to this drawing.

The sphygmomanometer shown in FIG. 1 includes a cuff 11, a pressure sensor 12, a pressurizing pump 13, a gradual exhaust unit 14, a rapid exhaust unit 15, an A / D converter 16, an operation input device 17, an output unit 18, and a display. 19 and the power supply device 20 are provided in the same manner as the conventional sphygmomanometer shown in FIG.
0 is provided.

The arithmetic unit 10 performs various arithmetic processes using the digital signal converted by the A / D converter 16 in accordance with the operation input performed by the operation input unit 17, and performs the operation of the pressurizing pump 13 and gradually. Control for the exhaust unit 14 and the rapid exhaust unit 15 and the output unit 18 and the display 1
9 and an output control for the cuff pressure extracting unit 10.
2. The functions of the storage unit 103, the calculation unit 104, the exhaust speed pulse rate monitor 106, and the cuff pressure monitor 107 are shown in FIG.
As in the conventional blood pressure monitor shown in FIG.

The arithmetic unit 10 has the following functions as differences from the above-mentioned conventional sphygmomanometer. That is, the extracted data is stored in the storage unit 103 and the characterization as a characterization setting unit that performs characterization of data obtained from the A / D converter 16 and sets blood pressure determination conditions according to the characterization data. An arterial pulse wave extraction unit 101 to be passed to the setting unit, a storage unit 110 for storing data from the arterial pulse wave extraction unit 101, and a segmented pulse wave for calculating the values of the added pulse wave and the segmented pulse wave from the data. A calculating unit 111, a calculating unit 112 for comparing values obtained from the added pulse wave and the segmented pulse wave, a stratifying unit 113 for stratifying data according to the comparison result, and a stratified stratum. Stratified calculation determining unit 114 for setting blood pressure determination conditions
And a blood pressure determination unit 105 that performs blood pressure determination using the set (changed or selected) blood pressure determination condition and displays the determination result on the display 19.

Next, the operation of the characterization setting means of this embodiment, which is different from the conventional one, will be briefly described. If data is taken into the characterization setting means from the A / D converter 16 via the arterial pulse wave extraction unit 101, Characterization of the data is performed. Thereafter, the blood pressure determination condition is selected according to the result of the characterization.

As a result, the blood pressure determination using the selected blood pressure determination condition is performed by the blood pressure determination unit 105, and the optimal blood pressure determination according to the data can be performed. In the present embodiment, similarly to the conventional sphygmomanometer shown in FIG. 2, the arterial pulse wave extraction unit 101, the cuff pressure extraction unit 102, the storage unit 103, the calculation unit 104, the blood pressure determination unit 105, the exhaust speed pulse rate monitor 106 Since the cuff pressure monitor 107 is employed, the blood pressure can be determined optimally by calculation using the pulse wave value and the constant rate.

Hereinafter, various embodiments of the sphygmomanometer having the above-described configuration, which are different from the conventional ones, will be described sequentially with reference to the drawings.

FIG. 2 is a diagram showing one embodiment of the segmentation performed by the storage unit 110 and the segmentation pulse wave calculation unit 111 in FIG.

In the example of FIG. 2, first, data obtained from the A / D converter 16 via the arterial pulse wave extracting unit 101, that is, pulse pressure values W11 to Wpmax as pulse waves at predetermined sampling intervals are calculated as follows. As shown in FIG. 2B, the data is stored in the storage unit 111 in such a manner that the order of capture is maintained.
It is memorized. In the example of FIG. 2, the data of the pulse wave 1 is W11 to W11.
1n (W1max), pulse wave 2 is W21 to W2m (W2max),.
Are stored in a table format for each row as WP1 to (Wpmax). Instead of capturing and storing each pulse wave at the maximum width as described above, for example, a configuration in which data in a predetermined range including the peak of each pulse wave may be stored.

Next, the starting point t1 to the ending point tM of each pulse wave.
At each sampling interval in the pulse width up to AX, the respective values of pulse waves 1 to P are summed. In the example of FIG. 2, (b)
The pulse pressure values W11, W21, W31,..., W at the start point t1 shown in FIG.
The sum of P1 is obtained as an added pulse wave at the start point t1 by the arithmetic expression shown at the start point t1 in (c). t2 point to end point t
The added pulse wave of MAX is calculated in the same manner as the added pulse wave of the start point t1. When all the added pulse waves from the start point t1 to the end point tMAX are calculated, the sum of all the added pulse waves is obtained as the total added value of the added pulse waves.

Next, the added pulse wave from the start point t1 to the end point tMAX is subdivided into segmented pulse waves (addition pulse waves) at points tq to tr, and the sum of the subdivided pulse waves at points tq to tr is calculated. It is obtained as the total sum of the segmented pulse waves. Where tq to tr
Is included in the range of t1 to tMAX.

Here, the designation of the subdivided pulse wave is defined as a subdivided pulse wave from the added pulse wave.

Thereafter, for example, by comparing the total added value of the added pulse wave with the total added value of the subdivided pulse wave, stratification of data is performed, and a blood pressure determination formula is set for each stratified layer. Processing is performed. It should be noted that the present invention is not limited to the above, and a comparison of sums of peak values may be performed.

FIG. 3 is a diagram showing another embodiment of the segmentation performed by the storage unit 110 and the segmentation pulse wave calculation unit 111 in FIG. However, the continuous pulse waves 1, 2, ..., P shown in Fig. 3A are the same as those shown in Fig. 2A.

In the example of FIG. 3, first, as in FIG.
The data obtained from the A / D converter 16 via the arterial pulse wave extraction unit 101 is stored and stored in the storage unit 111 so as to maintain the order of acquisition, as shown in FIG.

Next, as shown in FIG. 3C, at each sampling interval in the pulse wave width from the start point t1 to the end point tMAX of each pulse wave, each value of the pulse waves 1 to P is added to the added pulse wave. Are summed as

Next, the pulse pressure values at the start point t1 to the end point tMAX shown in FIG. 3B are subdivided into the pulse pressure values at the points tq to tr as shown in FIG. T for each pulse wave
The sum of the pulse pressure values at points q to tr is obtained. That is, the sum total of each subdivided pulse pressure value of the pulse wave 1 from the point tq to the point tr is obtained by adding W1q +... + W1r. Pulse waves 2 to P are processed in the same manner as pulse wave 1. Thereafter, when the total sum of the subdivided pulse pressure values at points tq to tr for all the pulse waves is obtained, the total added value thereof is obtained as the total added value of the subdivided pulse waves.

Here, the designation of the segmented pulse wave is defined as a segmentation process from each individual pulse wave.

After that, for example, by comparing the added pulse wave with the total added value of the segmented pulse wave, stratification of data is performed, and processing for setting a blood pressure judgment formula for each stratified layer is performed. . It should be noted that the present invention is not limited to the above, and a comparison of sums of peak values may be performed.

FIG. 4 is a diagram showing an embodiment of the extraction by the arterial pulse wave extraction unit 101 in FIG. In the example of FIG.
The pressure is reduced in steps, and a pulse wave is extracted when the pressure is held in each step. This makes it easier to extract the pulse wave being measured. In this case, the blood pressure monitor is configured such that the arithmetic unit 10 functioning as such an arterial pulse wave extracting unit extracts a pulse wave while gradually controlling the exhaust unit 14 as shown in FIG. Needless to say.

FIG. 5 is a diagram showing another embodiment of the extraction by the arterial pulse wave extraction unit 101 in FIG. 1. In the example of FIG. 5, a variable speed decompression method is adopted. That is, when a pulse wave appears in the process of pressure reduction, the pressure reduction speed is reduced, and the pulse wave is extracted when the pressure change gradient is gentle. This allows
Pulse waves during measurement can be easily extracted.

FIG. 6 is a diagram showing one embodiment of the base line used in the arterial pulse wave extracting unit 101 in FIG. In the example of FIG. 6, a straight line connecting the pulse wave start point and the pulse wave end point (next pulse wave start point) is determined as a reference line, that is, a base line.
A pulse wave is extracted using this baseline. That is, it is devised so that a necessary pulse wave is not cut off at the time of pulse wave extraction.

FIG. 7 is a diagram showing another embodiment of the base line used in the arterial pulse wave extracting unit 101 of FIG. In the example of FIG. 7, the baseline is determined by the previous pressurization or exhaust information.
That is, a straight line connecting the start point and the end point of the previous pulse wave is used as a baseline from which the current pulse wave is extracted. It is designed so that a necessary pulse wave is not cut off when extracting a pulse wave.

FIG. 8 is a diagram showing another embodiment of the base line used in the arterial pulse wave extracting unit 101 in FIG. In the example of FIG. 8, the base line is determined as a straight line parallel to the time axis from the start point of the next pulse wave (end point of the current pulse wave). It is designed so that a necessary pulse wave is not cut off when extracting a pulse wave.

FIG. 9 is a diagram showing one embodiment of pulse wave extraction by the arterial pulse wave extraction unit 101 in FIG. However, FIG.
9B shows a waveform of a signal obtained by applying a digital filter to the signal shown in FIG. 9A to remove a low frequency component.

In the example shown in FIG. 9, in order to extract a pulse wave, the static pressure information of the cuff is removed from the cuff pressure information being measured by a high-frequency band-pass filter. After the determination, the pulse wave required at the time of extracting the pulse wave is devised so as not to be cut off.

In this case, the configuration may be such that the frequency band of the filter is set to 1 Hz or less. Thereby, components near DC can be removed without removing the pulse wave components (so that necessary pulse waves are not cut off).

Further, a filter having a Chebyshev type cut-off characteristic may be employed as the filter. As a result, it is possible to separate the artifact and the pulse wave component, and there is an advantage that the information in proximity can be separated.

Further, the filter may be digitized and formed into a microcomputer. As a result, the microcomputer can be integrated with the microcomputer for blood pressure determination, and the hardware configuration can be simplified. Also, without such integration, the arterial pulse wave extraction unit 1
The above-described filter may be provided between the input terminal of the arithmetic unit 10 corresponding to the input of “01” and the A / D converter 16.

FIG. 10 is a diagram showing one embodiment of data restriction on the storage unit 110 of FIG. Data stored in the storage unit 110 is limited to fixed-length data. FIG.
The example of FIG. 7 shows that data of a portion exceeding a fixed length is to be deleted from the data once stored in the storage unit 110. As the setting of the fixed length, for example, in consideration of the pulse rate and the sampling time, when the pulse rate is 30 beats / minute and the sampling time is 20 ms, the fixed length is set to 100.
Then, the memory length can be fixed without deleting the pulse wave data.

FIG. 11 is a diagram showing an embodiment of the fixed length determining method related to FIG. For example, in order to determine the fixed length of the pulse wave, several pulse waves (five pulse waves in FIG. 11) are considered for the fixed length calculation from the pulse wave extraction start point (provisionally determined), and the pulse wave width of the several pulse waves is calculated. Then, the fixed length is finally determined. According to this method, there is an advantage that the width of the pulse wave can be set according to each data.

Further, as shown in FIG. 11 and the following equation, the fixed length may be determined based on the average value of the widths of several pulse waves.

Average value = (wavelength 1 + wavelength 2+... + Wavelength 5) / 5 As shown in FIG. 11 and the following equation, as the calculation of the fixed length from the pulse wave, the median value of the width of the pulse wave is used. The fixed length may be determined.

Median (median value) = 38 (wavelength 2) In this case, when the width of some of the plurality of pulse waves becomes extremely large or small due to the influence of noise, the average value is obtained. , The influence of the noise can be reduced.

Further, as shown in FIG. 11 and the following equation,
The fixed length may be determined in consideration of the average value or the extra median value so that all data is not deleted as much as possible.

Additional fixed length = (average or median)
× (1 + surcharge rate) FIGS. 12 to 14 are diagrams showing an embodiment of a method for selecting several pulse waves with reference to FIG.

For example, several pulse waves around the pulse wave extraction start point other than the pulse wave appearance start point as shown in FIG.
As shown in (b), it may be selected as a several pulse wave for determining the above-mentioned fixed length. Note that the fixed length determining means may be the example described with reference to FIG. 11, but a baseline from which a pulse wave is cut out from exhaust or pressurization information is determined from previous measurement data, and the fixed length is determined by the cut out width. A method of determining may be used.

Further, as shown in FIG. 13 (b), several pulse waves near the maximum pulse wave as shown in FIG. 13 (a) are converted into several pulse waves for determining the fixed length described with reference to FIG. You may make it select as a wave.

In short, as shown in FIG. 14 (a), at least a part of the vicinity of the pulse wave extraction start point, the vicinity of the maximum pulse wave and the vicinity of the measurement end point is shown in FIGS. 14 (b) to (d). Such a pulse wave may be selected.

FIG. 15 is a diagram showing another embodiment of the data restriction on the storage unit in FIG. In the example of FIG. 15, the fixed length of the pulse wave width is determined in advance when calculating the fixed length of the pulse wave width in order to limit the memory and reduce the load due to the calculation. , Data below the threshold value are deleted.

FIG. 16 is a diagram showing an embodiment of thinning. The sampling data as shown in FIG. 16A from the A / D converter 16 is thinned out to the data as shown in FIG. 16B for memory limitation and stratified calculation. The thinning rate may be thinned, for example, every one sample time, or may be thinned every two sample times.

FIG. 17 is a diagram showing an embodiment of a pulse wave range necessary for obtaining an added pulse wave. In the example of FIG. 17, all the extracted data are added as conditions for adding the added pulse wave. Shows the state of the object. Obtaining the added pulse wave in this way simplifies the calculation means and maximizes the S / N ratio of the obtained added pulse wave.

FIG. 18 is a diagram showing another embodiment of the pulse wave range necessary for obtaining an added pulse wave. The example of FIG. 18 shows that the extracted data has a size larger than a certain threshold value. This shows that a pulse wave having is subject to addition. If the added pulse wave is obtained in this way, the noise component can be reduced.
In addition, as a method of setting the threshold value, the area value, width,
The peak value can be considered.

FIG. 19 is a diagram showing another embodiment of a pulse wave range necessary for obtaining an added pulse wave. If only several pulse waves during measurement are to be added, the calculation load can be reduced. FIG.
The example of No. 9 shows a state in which the data of the maximum peak and its neighboring data are to be added.

FIG. 20 is a diagram showing another embodiment of a pulse wave range necessary for obtaining an added pulse wave. In addition to the above example, FIG.
As indicated by 0, data near the systolic blood pressure and near the diastolic blood pressure may be set in a pulse wave addition target range for obtaining an additional pulse wave.

FIG. 21 is a diagram showing one embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 21, the maximum value of the pulse wave is used for judging whether the pulse wave is effective or not. The peak value is used. However, the present invention is not limited to this, and the peak value of the specific part of the pulse wave may be used.

FIG. 22 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. The peak value from the point level, that is, the relative value is used. Note that FIG.
In the example of 2, the relative value is the maximum, but the relative peak value of the specific part of the pulse wave may be used.

FIG. 23 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 23, the next pulse wave is used for judging whether the pulse wave is effective or not. Is used relative to the starting point of. It should be noted that the relative peak value of the specific part of the pulse wave may be used instead of the maximum relative value.

FIG. 24 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example shown in FIG. A relative value from the baseline determined by the start point and the end point of the pulse wave (start point of the next pulse wave) is used. It should be noted that the relative peak value of the specific part of the pulse wave may be used instead of the maximum relative value.

Although the peak value is used for the above-mentioned validity determination, the present invention is not limited to the peak value, and a method using time (size in the time axis direction) as the width of the pulse wave may be used. Hereinafter, various embodiments of this method will be described.

FIG. 25 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 25, the judgment of whether the pulse wave is effective or not is made. The maximum pulse wave width that is cut from the starting point by a straight line parallel to the time axis direction is used. It should be noted that the pulse width may be a width obtained by cutting at a specific portion instead of the maximum pulse wave width.

FIG. 26 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. The maximum pulse wave width cut off by a straight line determined by the start point and the end point (start point of the next pulse wave) is used. Note that the width may not be the maximum pulse wave width but may be the width of a specific portion parallel to the straight line when cut out.

Further, the present invention is not limited to the above-described amplitude width, and a method may be used in which the magnitude of the area value of the pulse wave is used as a criterion for determining the effectiveness. The area value may be defined by adding sampling data or approximating a triangle area (maximum peak value × maximum width). Hereinafter, various embodiments of this method will be described.

FIG. 27 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 27, the judgment of whether the pulse wave is effective or not is made. An area value surrounded by a straight line parallel to the time axis direction from the start point and a pulse wave is used. As the definition of the area value, addition processing of sampling data or approximation of a triangle area (maximum peak value × maximum width as a relative value from a straight line) can be considered. It is not necessary to use the start point of the pulse wave as a reference. For example, an area value surrounded by a straight line parallel to the time axis direction and a pulse wave from a point at which a certain threshold value has risen from the start point may be used.

FIG. 28 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 28, the judgment of whether the pulse wave is effective or not is made. An area value surrounded by a straight line determined by the start point and the end point (start point of the next pulse wave) and the pulse wave is used. As the definition of the area value, addition processing of sampling data or approximation of a triangle area (maximum peak value × maximum width as a relative value from a straight line) can be considered. It is not always necessary to be the start point of the pulse wave. For example, the start point may be a point at which the threshold value has risen from the start point.

FIG. 29 is a diagram showing another embodiment of the judgment value used for judging the validity of the pulse wave. In the example of FIG. 29, the judgment of whether the pulse wave is effective or not is made. A perpendicular line passing through the start point, a straight line parallel to the time axis from the start point of the next pulse wave, and an area value surrounded by the pulse wave are used. As the definition of the area value, addition processing of sampling data or approximation of a triangle area (maximum peak value × maximum width as a relative value from a straight line) can be considered. Note that it is not always necessary to be the start point of the next pulse wave, and it may be a point at which a certain threshold value has risen from the start point.

FIG. 30 is a diagram showing an embodiment of processing of a pulse wave that has been invalidated by the validity determination. In the example of FIG. 30, data of the invalidated pulse wave is deleted.

FIG. 31 is a diagram showing another embodiment of the processing of the pulse wave invalidated by the validity judgment. Data of the invalidated pulse wave is connected to the front pulse wave as a part of the front pulse wave. Is made. In the example of FIG. 31, the end point of the previous pulse wave connected to the start point of the invalid pulse wave and the start point of the next pulse wave connected to the end point of the invalid pulse wave are connected.

FIG. 32 is a diagram showing an embodiment of a method of processing the area value obtained after the baseline correction. In the example of FIG. 32,
The area value obtained after the baseline correction as shown in FIG.
As shown in (b), one negative sampling value is converted into a sign-signed absolute value and processed.

FIG. 33 shows another embodiment of a method for processing the area value obtained after the baseline correction. In the example of FIG. 33, the area value obtained after the baseline correction as shown in FIG. , (B), one sampling value that has become a negative value is processed with a zero value.

FIG. 34 shows an embodiment of the segmentation of the added pulse. In the example of FIG. 34, a partial pulse wave cut by one straight line perpendicular to the time axis is selected as the segmentation pulse wave. Is shown.

FIG. 35 is a diagram showing another embodiment of the segmentation of the added pulse. In the example of FIG. 35, the partial pulse wave including the maximum peak value cut by one straight line perpendicular to the time axis is segmented. It becomes a pulse wave. It should be noted that a partial pulse wave in the vicinity thereof may be used without including the maximum peak value.

FIG. 36 is a diagram showing another embodiment of the segmentation of the added pulse. In the example of FIG. 36, a partial pulse wave cut by a plurality of straight lines perpendicular to the time axis is a segmented pulse wave.

FIG. 37 is a diagram showing another embodiment of the segmentation of the added pulse. In the example of FIG. 36, the partial pulse wave including the maximum pulse value cut by a plurality of straight lines perpendicular to the time axis is segmented. It becomes a pulse wave. It should be noted that a partial pulse wave in the vicinity thereof may be used without including the maximum peak value.

FIG. 38 is a diagram showing one embodiment of the comparison performed by the arithmetic unit 112 of FIG. 1. In the example of FIG.
A state is shown in which a comparison is made between the whole pulse wave as shown in (a) and the segmented pulse wave as shown in (b).

FIG. 39 is a diagram showing another embodiment of the comparison performed by the arithmetic unit 112 of FIG. 1. In the example of FIG.
A comparison is made between the segmented pulse wave, which is the left part of the whole pulse wave as shown in FIG. 7A, and the segmented pulse wave which is the right part of the whole pulse wave, as shown in FIG.

FIG. 40 is a diagram showing another embodiment of the comparison performed by the arithmetic unit 112 of FIG. 1. In the example of FIG.
The comparison is made in terms of the area ratio (= the partial pulse wave of the added pulse / the entire added pulse) of the whole pulse wave shown in (a) and the segmented pulse wave which is the central part of the whole pulse wave shown in (b). Done.

FIG. 41 is a diagram showing another embodiment of the comparison performed by the arithmetic section 112 in FIG. 1. The comparison is performed based on the peak value ratio between the whole pulse wave and the partial pulse wave. In the example of FIG. 41, a state is shown in which the amplitude is the amplitude ratio of the peak value corresponding to the peak value of the whole pulse wave and the peak value corresponding to the extreme value of the valley of the whole pulse wave (= extreme value of valley / peak value). I have.

FIG. 42 is a diagram showing an embodiment of the stratification performed by the stratification unit 113 in FIG. 1. The comparison result by the arithmetic unit 112 is stratified by the stratification unit 113. In the example of FIG. 42, the area ratio is used for the comparison result by the calculation unit 112. Then, layers 1 to 4 are set from the lower area ratio to the higher area ratio, and different blood pressure determination conditions are assigned to these layers 1 to 4. Therefore, in this case, when the area ratio is obtained as a comparison result from the arithmetic unit 112, the data obtained from the A / D converter 16 is stratified by the stratification unit 113 into a layer corresponding to the area ratio. . As a result, the data obtained from the A / D converter 16 is assigned the blood pressure determination condition characterized by the data.

FIG. 43 is a view showing another embodiment of the stratification performed by the stratification unit 113 in FIG. 1. In the example of FIG. 43, the layer stratification by the stratification unit 113 is almost the same as that of FIG. It differs from the example of FIG. 42 in that it is determined redundantly (indefinitely) at another time. In other words, the boundaries between the layers 1 to 4 are
It is uncertain due to fuzzy inference, chaos, neuron, fractal or neuro inference, and, for example, if the area ratio from the arithmetic unit 112 is a value corresponding to the vicinity of the boundary between layer 1 and layer 2, A / D Converter 16
Are stratified into layers 1 and 2.

FIG. 44 is an explanatory diagram of a function for determining whether or not the area ratio is lower than the threshold value. In the example of FIG. 44, it is determined whether or not the area ratio is lower based on the threshold value. The situation is shown. For example, as a result of comparison of the obtained segmented pulse waves, it is determined whether the pulse wave is lower than the threshold value.

FIG. 45 is a diagram showing an embodiment in which a notification is made when it is determined that the area ratio is lower than the threshold value. In the example of FIG. 45, the switch of the sphygmomanometer is turned on as shown in FIG. Then, the measurement of blood pressure starts and, as shown in (b) and (c), when the area ratio falls below a predetermined threshold value, (d)
As shown in FIG. Thereby, as a result of the comparison of the segmented pulse waves, it is understood that the pulse wave is smaller than the threshold value.

FIG. 46 is a diagram showing an embodiment of the evaluation of the change in circulatory system information with respect to the area ratio. In the example of FIG. 46, the normal area, the symptom A area, the symptom B area and the symptom C area are determined according to the area ratio. Is evaluated. In addition, such a tendency,
Although it is obtained from the change of the segmented pulse wave or the whole pulse wave using the threshold value as a criterion as shown in FIG. 44, such a result may be recorded or reported.

FIG. 47 is a diagram showing an embodiment of the diagnosis of blood pressure. In the example of FIG. 47 (a), the diagnosis is made depending on the number of inflection points of the segmented pulse wave or the whole pulse wave. On the other hand, in the example of FIG. 47B, the diagnosis is performed based on the width of the pulse wave. The diagnosis may be performed based on the peak value or the like, or the diagnosis may be performed in consideration of other parameters.

FIG. 48 is a diagram showing an embodiment of subdivision of one pulse. In the example of this figure, each time one pulse of a continuous pulse wave as shown in (a) is obtained, one pulse is cut out by one straight line perpendicular to the time axis as shown in (b), and (c) ) And (d) show a manner of obtaining a partial pulse wave of one pulse. As described above, means for segmenting a pulse wave every time a pulse wave is obtained may be provided, and in particular, a partial pulse wave cut by one straight line perpendicular to the time axis may be set as a segmented pulse.

FIG. 49 is a diagram showing another embodiment of subdivision of one pulse. In the example of FIG. 49, every time one pulse of a continuous pulse wave as shown in FIG. 49A is obtained, one pulse is cut by two straight lines perpendicular to the time axis as shown in FIG. c) ~
(E) shows a manner of obtaining a single partial pulse wave such as a left part, a center part, and a right part shown in (e). As described above, means for segmenting a pulse wave every time a pulse wave is obtained may be provided, and a partial pulse wave cut by a plurality of straight lines perpendicular to the time axis may be used as a segmented pulse.

By configuring each part of the characterization setting means as described above and stratifying the data in accordance with the appearance pattern of the pulse wave of the data, the blood pressure judgment corresponding to the data can be performed.
Countermeasures can be taken against the above-mentioned problem in blood pressure determination.

[0141]

As is clear from the above, according to the first aspect of the present invention, means for performing A / D conversion and means for extracting biological information from the value after A / D conversion by this means. Means for storing the biological information extracted by the means, means for performing an operation using the biological information stored in the means, and means for determining blood pressure using the result of the operation by the means. A sphygmomanometer comprising: means for extracting a pulse wave during measurement, means for adding a plurality of pulse waves extracted by this means, means for subdividing the pulse wave after addition by this means, Means for comparing a pulse wave segmented by this means with a predetermined pulse wave, means for quantifying the comparison result by this means, and the A / D conversion based on the result of quantification by this means Means for stratifying the data obtained from the means into multiple layers Because and means for changing the calculation formula for determining the blood pressure in stratified by each layer in this way, can the blood pressure determination corresponding to the data, can be performed countermeasures against problems in the blood pressure determination described above.

According to the second aspect of the present invention, means for performing A / D conversion, means for extracting biometric information from a value after A / D conversion by this means, and means for extracting biometric information extracted by this means A sphygmomanometer comprising: means for storing; means for performing an operation using the biological information stored in the means; and means for determining blood pressure using the result of the operation performed by the means. Means for extracting a pulse wave, means for adding a plurality of pulse waves extracted by this means, means for segmenting and adding the extracted pulse wave, and means for segmenting and adding the pulse wave extracted by this means. Means for comparing a wave with a predetermined pulse wave, means for quantifying the comparison result by the means, and data obtained from the means for performing the A / D conversion based on the result of the quantification by the means. Means for stratifying into layers and stratified by this means Because and means for changing the calculation formula for determining the blood pressure in the layer, can blood pressure determination corresponding to the data, can be performed countermeasures against problems in the blood pressure determination described above.

According to the third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in order to extract a pulse wave, the operation of temporarily stopping the evacuation or pressurizing operation when a pulse wave appears and maintaining the pressure. By doing, since the pulse wave is cut out with the pulse wave start point as the reference point, without removing the necessary pulse wave component,
Extraction can be performed.

According to the fourth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in order to extract a pulse wave, the exhaust or pressurizing operation speed is reduced when a pulse wave appears,
Since the pulse wave is cut out with the pulse wave start point as a reference point in a state where the depressurized or pressurized state is gentle, extraction can be performed without removing a necessary pulse wave component.

According to the fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, when the pulse wave is extracted, the start point of the pulse wave and the start point of the next pulse wave are used as the baseline for extracting the pulse wave. Since the pulse wave is taken out as a straight line to be determined, extraction can be performed without removing necessary pulse wave components.

According to the sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, a straight line determined from pressure change information before the entire pulse is used as a baseline for extracting a pulse wave when extracting a pulse wave. Since the pulse wave is cut out, extraction can be performed without removing a necessary pulse wave component.

According to the seventh aspect of the present invention, in the sphygmomanometer according to the first or second aspect, when a pulse wave is extracted, a horizontal line in the time axis direction from the start point of the next pulse wave is obtained as a base line for extracting a pulse wave. Since the pulse wave is cut out by using the straight line, the extraction can be performed without removing the necessary pulse wave component.

According to the eighth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, at the time of extracting the pulse wave, the static pressure information included in the pressure pulse wave information is removed by a high-pass filter, and the pulse wave component is removed. Since only the dynamic pressure portion is extracted and a pulse wave is cut out using the zero point as a reference point, extraction can be performed without removing a necessary pulse wave component.

According to the ninth aspect of the present invention, in the sphygmomanometer according to the eighth aspect, since the cutoff frequency of the high-pass filter is 1 Hz or less, extraction can be performed without removing necessary pulse wave components.

According to the tenth aspect of the present invention, in the sphygmomanometer according to the eighth aspect, since the high-pass filter has a Chebyshev-type cutoff characteristic, extraction can be performed without removing a necessary pulse wave component.

According to the eleventh aspect of the present invention, in the sphygmomanometer according to the eighth aspect, since the function of the high-pass filter is digitized, microcomputer processing can be performed. Extraction can be performed without removing the pulse wave component.

According to the twelfth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, in the pulse wave extraction, the number of data to be extracted is limited to a predetermined number in order to limit the memory. The processing load can be reduced.

According to the thirteenth aspect of the present invention, in the sphygmomanometer according to the twelfth aspect, as the predetermined number of means, a plurality of pulse waves are taken out from the start of the measurement, and the time axis information as the pulse wave width of the several pulse waves is obtained. , The load on the arithmetic processing can be reduced.

According to the fourteenth aspect of the present invention, in the sphygmomanometer according to the thirteenth aspect, the predetermined number is determined based on the average value of the time axis information of several pulse waves as the calculating means, so that the load on the arithmetic processing is reduced. Becomes possible.

According to the fifteenth aspect of the present invention, in the sphygmomanometer according to the thirteenth aspect, the predetermined number is determined based on the median value of the time axis information of the several pulse waves as the calculating means, so that the load on the arithmetic processing is reduced. Becomes possible.

According to the sixteenth aspect of the present invention, in the sphygmomanometer according to the fourteenth or fifteenth aspect, since the increment is given in consideration of the average value and the median rate, the load on the arithmetic processing can be reduced. become.

According to the seventeenth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the present pressure change information is estimated from the past pressure change information except at the start point of the pulse wave. Since it is determined by a pressure change straight line or a pulse wave cut off by a curve, it is possible to reduce the load of arithmetic processing.

According to the eighteenth aspect of the present invention, in the sphygmomanometer according to any one of the twelfth to sixteenth aspects, a predetermined number of pulse waves are extracted from the vicinity of the maximum pulse wave and a predetermined number is determined. Reduction becomes possible.

According to the nineteenth aspect of the present invention, in the sphygmomanometer according to any one of the twelfth to sixteenth aspects, several pulse waves are extracted from near the start pulse wave, near the end pulse wave, and near the maximum pulse wave point. , A predetermined number is determined, so that the load on the arithmetic processing can be reduced.

According to the twentieth aspect of the present invention, in the sphygmomanometer according to the twelfth aspect, a predetermined number is temporarily determined in advance, and a predetermined threshold value of the portion is determined by comparing with a part of the added pulse wave. In the following case, a means for invalidating the data is provided, so that the load on the arithmetic processing can be reduced.

According to the twenty-first aspect of the present invention, in the sphygmomanometer according to the first or second aspect, an additional pulse for comparison,
Since there is a means for reducing the required memory capacity by subtracting the obtained sampling data for a predetermined period for the segmented vein, the load on the arithmetic processing can be reduced.

According to the twenty-second aspect of the present invention, in the sphygmomanometer according to the first or second aspect, since all the extracted pulse waves are added to be added and subdivided, the load of the arithmetic processing is increased. Reduction becomes possible.

According to the twenty-third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, only pulse waves having a magnitude equal to or greater than a predetermined threshold value are added and segmented. Calculation load can be reduced.

According to the twenty-fourth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, since several pulse waves are taken out near the maximum value of the pulse wave and added and segmented, the arithmetic processing is performed. Load can be reduced.

According to the twenty-fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, several pulse waves are taken out near the systolic blood pressure and the diastolic blood pressure value, and are subjected to addition and segmentation. Thus, the load on the arithmetic processing can be reduced.

According to the twenty-sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the pulse component is set based on the pulse wave peak value as a criterion for determining whether the pulse wave is valid or invalid. be able to.

According to the twenty-seventh aspect of the present invention, in the sphygmomanometer according to the twenty-sixth aspect, the peak value is defined by using the pulse wave starting point as the reference point, so that the noise component can be determined. it can.

According to the twenty-eighth aspect of the present invention, in the sphygmomanometer according to the twenty-sixth aspect, the peak value is defined by using the next pulse wave starting point as a reference point, so that the noise component is determined. Can be.

According to the twenty-ninth aspect of the present invention, in the sphygmomanometer according to the twenty-sixth aspect, the peak value is defined using a base line determined by a pulse wave start point and a next pulse wave start point as a reference line. Therefore, the noise component can be determined.

According to the thirtieth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the pulse wave width is set based on the time axis information as the pulse wave width as a criterion for determining whether the pulse wave is valid or invalid. The components can be determined.

According to the thirty-first aspect of the present invention, in the sphygmomanometer according to the thirty-third aspect, a portion cut off by a reference line parallel to a time axis determined at a start point of the pulse wave as a definition of the pulse wave width. Therefore, the noise component can be determined.

According to the thirty-second aspect of the present invention, in the sphygmomanometer according to the thirtieth aspect, the width of the pulse wave is defined by a reference line determined by a start point of the pulse wave and a start point of the next pulse wave. The noise component can be determined because the width is determined based on the partial width.

According to the thirty-third aspect of the present invention, in the sphygmomanometer according to the first or second aspect, the addition data of the quantized sampling value is set as the area value of the pulse wave as a criterion for determining whether the pulse wave is valid or invalid. Therefore, the noise component can be determined.

According to the thirty-fourth aspect of the present invention, in the sphygmomanometer according to the thirty-third aspect, a partial area cut off by a base line parallel to a time axis determined at a start point of a pulse wave as a definition of the area value. Therefore, the noise component can be determined.

According to the thirty-fifth aspect of the present invention, in the sphygmomanometer according to the thirty-third aspect, a partial area cut off by a base line determined by a start point of a pulse wave and a start point of a next pulse wave is defined as an area value. Since the noise area is determined by the appropriate area, the noise component can be determined.

According to the thirty-sixth aspect of the present invention, in the sphygmomanometer according to the thirty-third aspect, the partial value cut off by the base line parallel to the time axis determined at the start point of the next pulse wave as the definition of the area value. Since the area is determined, the noise component can be determined.

According to the thirty-sixth aspect of the present invention, in the sphygmomanometer according to any one of the twenty-sixth, thirty-sixth, and thirty-third aspects, when the invalidity of the pulse wave is determined as a result of the invalidity determination, the data of the invalid pulse wave is obtained. Is deleted, the noise component can be determined.

According to the thirty-eighth aspect of the present invention, in the sphygmomanometer according to any one of the twenty-sixth, thirty-third and thirty-third aspects, if the invalidity of the pulse wave is determined as a result of the invalidity determination of the pulse wave, Since it is combined with the pre-pulse wave data as a part of the pre-pulse wave, the noise component can be determined.

According to the thirty-ninth aspect of the present invention, in the sphygmomanometer according to the thirty-fifth aspect, the sampling data has an absolute value and does not take the sign into consideration after the baseline correction. For example, in the sphygmomanometer according to the thirty-fifth aspect, when the sampling data becomes a negative number after the baseline correction, a process of adding the value as a zero value is performed. In the sphygmomanometer, a portion cut by one straight line perpendicular to the time axis is shown as the definition of the segmented pulse wave, so that the blood pressure can be determined in accordance with the data, and the above-described problem in the blood pressure determination can be taken.

According to the invention of claim 42, in the sphygmomanometer according to claim 41, the cut-out area includes the portion following the maximum wave height, so that the blood pressure can be determined in accordance with the data, and the blood pressure can be determined. Countermeasures can be taken for the problem in the judgment.

According to the invention of claim 43, in the sphygmomanometer of the above-mentioned claim 41, a portion cut off by a plurality of straight lines perpendicular to the time axis is defined as the definition of the segmented pulse wave. The determination can be performed, and countermeasures can be taken for the above-described problem in the blood pressure determination.

According to the forty-fourth aspect, in the sphygmomanometer according to the forty-third aspect, the cut-out area includes a portion after the portion showing the maximum wave height, so that the blood pressure can be determined in accordance with the data, and Countermeasures can be taken for the problem in the judgment.

According to the forty-fifth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, since the entire pulse wave and the segmented pulse wave are compared as comparison targets, the blood pressure determination corresponding to the data is performed. And measures can be taken against the above-mentioned problem in blood pressure determination.

According to the forty-sixth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, since the segmented pulse wave and the segmented pulse wave are compared as comparison targets, the blood pressure monitor corresponding to the data is obtained. The determination can be performed, and countermeasures can be taken for the above-described problem in the blood pressure determination.

According to the forty-seventh aspect of the present invention, in the sphygmomanometer according to the forty-fifth or forty-sixth aspect, since the comparison is performed with the ratio of the area values, the blood pressure determination corresponding to the data can be performed. Countermeasures can be taken against the problem in blood pressure determination.

According to the forty-eighth aspect of the present invention, in the sphygmomanometer according to the forty-fifth or forty-sixth aspect, the comparison is performed using the ratio of the peak values of the segmented pulse wave and a part of the whole pulse wave. Blood pressure determination corresponding to the data can be performed, and countermeasures can be taken for the above-described problem in blood pressure determination.

According to the forty-ninth aspect of the present invention, in the sphygmomanometer according to the first or second aspect, stratification is performed based on a result of the comparison, and a blood pressure judgment condition is changed for each stratified layer to determine a blood pressure. Therefore, blood pressure determination corresponding to the data can be performed, and a countermeasure can be taken for the above-described problem in blood pressure determination.

According to the fifty-seventh aspect of the present invention, in the sphygmomanometer according to the forty-ninth aspect, since a redundant determination is made by using fuzzy inference or the like in the vicinity of each layer boundary, a blood pressure determination corresponding to data can be performed. Thus, it is possible to take countermeasures against the problem in the blood pressure determination described above.

According to the thirty-first aspect of the present invention, in the sphygmomanometer according to the thirty-seventh aspect or the thirty-eighth aspect, the case where each ratio exceeds a predetermined threshold value is detected, so that a blood pressure determination corresponding to data can be performed. Thus, it is possible to take countermeasures against the problem in the blood pressure determination described above.

According to the invention of claim 52, the sphygmomanometer according to claim 51 has means for detecting a case where each ratio exceeds a predetermined threshold value and notifying the result, so that the data A corresponding blood pressure determination can be performed, and countermeasures can be taken for the above-described problem in the blood pressure determination.

According to the invention of claim 53, the sphygmomanometer of claim 47 or 48 has means for recording the change of each ratio and evaluating the result, so that the blood pressure judgment corresponding to the data can be performed. And measures can be taken against the above-mentioned problem in blood pressure determination.

According to the 54th aspect of the present invention, in the sphygmomanometer according to the 1st or 2nd aspect, the blood pressure monitor has a function of capturing the number of inflection points of the pulse wave. And measures can be taken against the above-mentioned problem in blood pressure determination.

According to the invention of claim 55, in the sphygmomanometer according to the above-mentioned claim 2, a portion cut off by one straight line perpendicular to the time axis is defined as the segmented pulse wave.
Blood pressure determination corresponding to the data can be performed, and countermeasures can be taken for the above-described problem in blood pressure determination.

According to the invention of claim 56, in the sphygmomanometer according to the above-mentioned claim 2, a portion cut out by a plurality of straight lines perpendicular to the time axis is shown as a definition of the segmented pulse wave.
Blood pressure determination corresponding to the data can be performed, and countermeasures can be taken for the above-described problem in blood pressure determination.

[Brief description of the drawings]

FIG. 1 is a configuration diagram of a sphygmomanometer according to an embodiment of the present invention.

FIG. 2 is a diagram showing an embodiment of the segmentation particularly performed by the storage unit and the segmentation pulse wave calculation unit in FIG. 1;

FIG. 3 is a diagram showing another embodiment of the segmentation performed by the storage unit and the segmentation pulse wave calculation unit in FIG. 1 in particular.

FIG. 4 is a diagram showing an embodiment of extraction by an arterial pulse wave extraction unit in FIG. 1;

FIG. 5 is a diagram showing another embodiment of extraction by the arterial pulse wave extraction unit in FIG. 1;

FIG. 6 is a diagram showing one embodiment of a baseline used in the arterial pulse wave extraction unit of FIG. 1; .

FIG. 7 is a diagram showing another embodiment of the baseline used in the arterial pulse wave extraction unit in FIG. 1;

FIG. 8 is a diagram showing another embodiment of the baseline used in the arterial pulse wave extraction unit in FIG. 1;

FIG. 9 is a diagram showing one embodiment of pulse wave extraction by the arterial pulse wave extractor of FIG. 1;

FIG. 10 is a diagram showing one embodiment of data restriction on a storage unit in FIG. 1;

FIG. 11 is a diagram illustrating an embodiment of a method for determining a fixed length according to FIG. 10;

FIG. 12 is a diagram showing an embodiment of a method of selecting a pulse wave related to FIG. 11;

FIG. 13 is a diagram showing another embodiment of the method for selecting a pulse wave related to FIG. 11;

FIG. 14 is a diagram showing another embodiment of the method for selecting a pulse wave related to FIG. 11;

FIG. 15 is a diagram showing another embodiment of the data restriction on the storage unit in FIG. 1;

FIG. 16 is a diagram illustrating an embodiment of thinning.

FIG. 17 is a diagram showing an embodiment of a pulse wave range necessary for obtaining an added pulse wave.

FIG. 18 is a diagram showing another embodiment of a pulse wave range necessary for obtaining an added pulse wave.

FIG. 19 is a diagram showing another embodiment of a pulse wave range necessary for obtaining an added pulse wave.

FIG. 20 is a diagram showing another embodiment of a pulse wave range necessary for obtaining an added pulse wave.

FIG. 21 is a diagram illustrating an embodiment of a determination value used for determining the validity of a pulse wave.

FIG. 22 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 23 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 24 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 25 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 26 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 27 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 28 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 29 is a diagram showing another embodiment of the determination value used for determining the validity of the pulse wave.

FIG. 30 is a diagram illustrating an embodiment of processing of a pulse wave that has been invalidated by the validity determination.

FIG. 31 is a diagram showing another embodiment of the processing of the pulse wave invalidated by the validity determination.

FIG. 32 is a diagram illustrating an embodiment of a method for processing an area value obtained after baseline correction.

FIG. 33 is a diagram showing another embodiment of a method for processing the area value obtained after the baseline correction.

FIG. 34 is a diagram showing one embodiment of subdivision of an added pulse.

FIG. 35 is a diagram showing another embodiment of the segmentation of the added pulse.

FIG. 36 is a diagram showing another embodiment of the segmentation of the added pulse.

FIG. 37 is a diagram showing another embodiment of the subdivision of the added pulse.

FIG. 38 is a diagram showing one embodiment of comparison performed by the calculation unit of FIG. 1;

FIG. 39 is a diagram showing another embodiment of the comparison performed by the calculation unit of FIG. 1;

FIG. 40 is a diagram showing another embodiment of the comparison performed by the calculation unit in FIG. 1;

FIG. 41 is a diagram illustrating another embodiment of the comparison performed by the calculation unit in FIG. 1;

FIG. 42 is a diagram illustrating an embodiment of stratification performed in the stratification unit of FIG. 1;

FIG. 43 is a diagram showing another embodiment of the stratification performed in the stratification unit of FIG. 1;

FIG. 44 is an explanatory diagram of a function of determining whether an area ratio is lower than a threshold value.

FIG. 45 is a diagram showing an embodiment in which a notification is made when it is determined that the area ratio is lower than the threshold value.

FIG. 46 is a diagram showing an embodiment of evaluation of a change in circulatory system information with respect to an area ratio.

FIG. 47 is a diagram showing an embodiment of blood pressure diagnosis.

FIG. 48 illustrates one embodiment of subdivision of a pulse.

FIG. 49 illustrates another embodiment of subdivision of a pulse.

FIG. 50 is a configuration diagram of a conventional sphygmomanometer.

FIG. 51 is a diagram showing the internal configuration and the like of the arithmetic unit shown in FIG. 50;

FIG. 52 is an explanatory diagram of the processing performed by the arithmetic unit shown in FIG. 50;

[Explanation of symbols]

 Reference Signs List 101 arterial pulse wave extraction unit 102 cuff pressure extraction unit 103 storage unit 104 calculation unit 105 blood pressure determination unit 106 exhaust speed pulse rate monitor 107 cuff pressure monitor 110 storage unit 111 subdivided pulse wave calculation unit 112 calculation unit 113 stratification unit 114 layer Separate calculation decision unit

 ──────────────────────────────────────────────────続 き Continuing from the front page (72) Inventor Haruhiro Terada 1048 Kazuma Kadoma, Kadoma-shi, Osaka Matsushita Electric Works Co., Ltd. F-term (reference) 4C017 AA08 AA09 AC03 BB12 BC07 BC11 BC14 FF15

Claims (56)

[Claims] A means for performing A / D conversion; a means for extracting biometric information from a value after A / D conversion by the means; a means for storing biometric information extracted by the means; A blood pressure monitor including means for performing an operation using the stored biological information, and means for determining a blood pressure using a result of the operation by the means, wherein a means for extracting a pulse wave during measurement; Means for adding a plurality of pulse waves extracted by this means, means for subdividing the pulse wave added by this means, and comparison between the pulse wave subdivided by this means and a predetermined pulse wave Means for quantifying the result of comparison by this means; means for stratifying data obtained from the means for performing A / D conversion into a plurality of layers based on the result of quantification by this means; For determining blood pressure in each layer stratified by Sphygmomanometer and means for changing the. 2. A means for performing A / D conversion, a means for extracting biometric information from a value after A / D conversion by this means, a means for storing biometric information extracted by this means, Means for performing an operation using the stored biological information, and a blood pressure monitor including means for performing a blood pressure determination using the calculation result by this means, and a means for extracting a pulse wave during measurement, A means for adding a plurality of pulse waves extracted by this means, a means for segmenting and adding the extracted pulse wave, and a pulse wave segmented and added by this means and a predetermined pulse wave. Means for comparing, means for quantifying the result of comparison by this means, means for stratifying data obtained from the means for performing A / D conversion based on the result of quantification by this means into a plurality of layers, For determination of blood pressure in each layer stratified by this means A blood pressure monitor comprising means for changing the calculation formula. 3. Extraction of a pulse wave based on a pulse wave start point as a reference point by performing an operation of temporarily stopping an exhausting or pressurizing operation when a pulse wave appears and performing a pressure holding operation for extracting a pulse wave. The blood pressure monitor according to claim 1. 4. Extraction of a pulse wave is performed by lowering the exhaust or pressurizing operation speed at the time of appearance of the pulse wave and gradually reducing the pressure or increasing the pressure when the pulse wave appears. The sphygmomanometer according to claim 1, wherein the blood pressure is cut out. 5. The sphygmomanometer according to claim 1, wherein when extracting the pulse wave, the pulse wave is extracted as a base line for extracting the pulse wave, which is a straight line determined by the start point of the pulse wave and the start point of the next pulse wave. 6. The sphygmomanometer according to claim 1, wherein a pulse wave is cut out by setting a straight line determined from pressure change information before all pulses as a base line for extracting a pulse wave when extracting a pulse wave. 7. The sphygmomanometer according to claim 1, wherein a pulse wave is extracted by setting a straight line obtained as a horizontal line in a time axis direction from a start point of the next pulse wave as a baseline for extracting a pulse wave when extracting a pulse wave. . 8. A high-pass filter removes static pressure information included in pressure pulse wave information at the time of extracting a pulse wave, extracts only a dynamic pressure portion as a pulse wave component, and cuts out a pulse wave with a zero point as a reference point. The blood pressure monitor according to claim 1. 9. The cut-off frequency of a high-pass filter is 1 Hz.
9. The sphygmomanometer according to claim 8, wherein: 10. The sphygmomanometer according to claim 8, wherein the high-pass filter has a Chebyshev-type blocking characteristic. 11. The sphygmomanometer according to claim 8, wherein microcomputer processing can be performed by digitizing the function of the high-pass filter. 12. The sphygmomanometer according to claim 1, wherein the number of data to be extracted is limited to a predetermined number in order to add a memory limit in the pulse wave extraction. 13. The sphygmomanometer according to claim 12, further comprising, as the predetermined number of determination means, means for extracting several pulse waves from the start of the measurement and calculating from time axis information as a pulse wave width of the several pulse waves. 14. The sphygmomanometer according to claim 13, wherein a predetermined number is determined based on an average value of time axis information of several pulse waves as the calculating means. 15. The sphygmomanometer according to claim 13, wherein the predetermined number is determined based on the median value of the time axis information of the pulse wave as the calculating means. 16. Considering an average value and a median premium rate,
A sphygmomanometer according to claim 14 or 15, which provides an increment. 17. The method according to claim 1, wherein the current pressure change information is estimated from the past pressure change information at a position other than the start point of the pulse wave, and the current pressure change information is determined by the estimated pressure change straight line or a pulse wave cut off by a curve. Sphygmomanometer. 18. The sphygmomanometer according to claim 12, wherein several pulse waves are taken out from the vicinity of the maximum pulse wave and a predetermined number is determined. 19. The sphygmomanometer according to claim 12, wherein a predetermined number of pulse waves are determined by extracting several pulse waves from near the start pulse wave, near the end pulse wave, and near the maximum pulse wave point. 20. A means for temporarily determining a predetermined number in advance and, by comparing with a part of the added pulse wave, means for invalidating the data when the value falls below a certain threshold value of the part.
Sphygmomanometer as described. 21. The sphygmomanometer according to claim 1, further comprising means for reducing the required memory capacity by subtracting sampling data obtained for the added pulse and subdivided pulse for comparison for a predetermined time. 22. By adding all the extracted pulse waves,
3. The sphygmomanometer according to claim 1, which is subject to addition and segmentation. 23. The sphygmomanometer according to claim 1, wherein only pulse waves having a magnitude equal to or greater than a predetermined threshold are added and segmented. 24. The sphygmomanometer according to claim 1, wherein several pulse waves are taken out in the vicinity of the maximum value of the pulse wave, added, and segmented. 25. The sphygmomanometer according to claim 1, wherein several pulse waves are taken out in the vicinity of the systolic blood pressure and the diastolic blood pressure value, and added and segmented. 26. The sphygmomanometer according to claim 1, wherein a pulse wave peak value is set as a criterion for determining whether the pulse wave is valid or invalid. 27. The sphygmomanometer according to claim 26, wherein the peak value is defined by a value based on the pulse wave starting point as a reference point. 28. The sphygmomanometer according to claim 26, wherein the peak value is defined by a value using the next pulse wave start point as a reference point. 29. The sphygmomanometer according to claim 26, wherein the peak value is defined by a value using a base line determined by the pulse wave start point and the next pulse wave start point as a reference line. 30. The sphygmomanometer according to claim 1, wherein the criterion of validity / invalidity of the pulse wave is set based on time axis information as the width of the pulse wave. 31. The sphygmomanometer according to claim 30, wherein the width of the pulse wave is defined by a partial width cut by a reference line parallel to a time axis determined at a start point of the pulse wave. 32. The sphygmomanometer according to claim 30, wherein the width of the pulse wave is defined by a partial width cut by a reference line determined by a start point of the pulse wave and a start point of the next pulse wave. 33. The sphygmomanometer according to claim 1, wherein the addition data of the quantized sampling value is set as the area value of the pulse wave as a criterion for determining whether the pulse wave is valid or invalid. 34. The sphygmomanometer according to claim 33, wherein the area value is determined by a partial area cut by a base line parallel to a time axis determined at a start point of the pulse wave. 35. The sphygmomanometer according to claim 33, wherein the area value is defined by a partial area cut by a baseline determined by a start point of the pulse wave and a start point of the next pulse wave. 36. The sphygmomanometer according to claim 33, wherein the area value is defined by a partial area cut by a base line parallel to the time axis determined at the start point of the next pulse wave. 37. The sphygmomanometer according to claim 26, wherein the invalid pulse wave data is deleted when the invalidity is determined as a result of the invalidity determination of the pulse wave. 38. The pulse wave data according to claim 26, wherein the invalid pulse wave is invalidated as a part of the pre-pulse wave and is combined with the pre-pulse wave data as a result of the invalidation of the pulse wave. Sphygmomanometer as described in. 39. The sphygmomanometer according to claim 35, wherein after the baseline correction, the sampling data takes an absolute value and does not consider the sign. 40. The sphygmomanometer according to claim 35, wherein when the sampling data becomes a negative number after the baseline correction, a process of adding the value as a zero value is performed. 41. The sphygmomanometer according to claim 1, wherein a portion cut off by one straight line perpendicular to the time axis is defined as the segmented pulse wave. 42. The sphygmomanometer according to claim 41, wherein the cut-out area includes a portion after the portion showing the maximum wave height. 43. The sphygmomanometer according to claim 1, wherein a portion cut out by a plurality of straight lines perpendicular to the time axis is defined as the definition of the segmented pulse wave. 44. The sphygmomanometer according to claim 43, wherein the cut-out area includes a portion after the portion showing the maximum wave height. 45. The sphygmomanometer according to claim 1, wherein the whole pulse wave is compared with the segmented pulse wave as a comparison target. 46. The sphygmomanometer according to claim 1, wherein the segmented pulse wave and the segmented pulse wave are compared as comparison targets. 47. The sphygmomanometer according to claim 45, wherein the comparison is carried out with the ratio of area values. 48. The sphygmomanometer according to claim 45, wherein the comparison is performed by using the ratio of the peak value of one part of the segmented pulse wave and the whole pulse wave. 49. The sphygmomanometer according to claim 1, wherein stratification is performed based on a result of the comparison, a blood pressure judgment condition is changed for each stratified layer, and blood pressure judgment is performed. 50. The sphygmomanometer according to claim 49, wherein a redundant determination is made using fuzzy inference or the like near the boundary between the layers. 51. The sphygmomanometer according to claim 47, wherein the case where each ratio exceeds a predetermined threshold value is detected. 52. The sphygmomanometer according to claim 51, further comprising means for detecting a case where each ratio exceeds a predetermined threshold and notifying the result. 53. The sphygmomanometer according to claim 47, further comprising means for recording a change in each ratio and evaluating the result. 54. The sphygmomanometer according to claim 1, wherein the sphygmomanometer has a function of capturing the number of inflection points of the pulse wave. 55. The sphygmomanometer according to claim 2, wherein a portion cut out by one straight line perpendicular to the time axis is defined as the segmented pulse wave. 56. The sphygmomanometer according to claim 2, wherein a portion cut out by a plurality of straight lines perpendicular to the time axis is defined as the segmented pulse wave.