JP2010017299A - Blood pressure measuring method and blood pressure measuring apparatus using this method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a blood pressure measuring method and a blood pressure measuring apparatus using the method by which a blood pressure can be measured at both of resting time and exercising time, especially, to provide the blood pressure measuring method and the blood pressure measuring apparatus using the method by which the same result as in the case that Korotkoff sounds are accurately measured can easily be acquired. <P>SOLUTION: This blood pressure measuring method has a pressed pulse wave measuring process (A), a specified frequency waveform extracting process (B), and a blood pressure value determining process (C). In this case, in the pressed pulse wave measuring process (A), a distortion sensor is arranged and fixed in a manner to be located on the inside of the cuff, and also, on the inside of the upper limb center of a human body. After the cuff is pressurized, the pressed pulse wave on the inside of the cuff is measured by the distortion sensor while decompressing the pressurization. In the specified frequency waveform extracting process (B), only pressed pulse waves of a specified frequency component for which the frequency becomes 100 Hz or lower are extracted from the pressed pulse wave which has been measured in the pressed pulse wave measuring process. In the blood pressure value determining process (C), a maximum blood pressure value or a minimum blood pressure value of the human body is determined conforming to the pressed pulse wave of the specified frequency component. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a blood pressure measurement method and a blood pressure measurement device using the method, and in particular, a blood pressure measurement method that is consistent with blood pressure measurement by Korotkoff sound, and that can measure blood pressure both at rest and during exercise, and its The present invention relates to a blood pressure measurement device using the method.

  At present, as a blood pressure measurement method, a measurement method using Korotkoff sound is standard. A cuff band is wrapped around the upper arm, air is introduced into the cuff band, and the blood vessel is compressed with a cuff pressure exceeding the maximum blood pressure. Then, while gradually lowering the pressure in the cuff, apply a stethoscope to the inner side of the elbow-line extension medial line at a distance of 2 to 3 cm from the cuff band attachment point and listen for Korotkoff sounds. The systolic blood pressure is when the Korotkoff sound occurs, and the systolic blood pressure is when the Korotkoff sound disappears.

  However, various sounds are generated in the living body and propagate through the body. In addition, the measurement environment is not necessarily a quiet environment, and skillful techniques are necessary to always measure Korotkoff sounds accurately. Even in the dynamics of exercise, it is difficult for an expert to accurately measure blood pressure. there were.

On the other hand, as shown in Patent Document 1, the present inventor has a projection wave (a part in which a sharp convex shape and a concave waveform are generated in the pulse waveform, as seen in the waveform of the compressed pulse by the sensor attached to the cuff inside. Focusing on the spike signal), and measuring the timing of the occurrence and disappearance of the protrusion and the timing of the occurrence and disappearance of the Korotkoff sound, It was shown that it can be measured.
Japanese Patent No. 3842390

  On the other hand, because the Korotkoff sound changes depending on the characteristics of the subject such as the thickness of the arm, blood pressure value, pulsation strength, presence or absence of arrhythmia, presence or absence of heart failure, abnormal blood pressure drop, etc., and the pressure of the stethoscope, Even with precise auscultation, it was difficult to accurately identify systolic blood pressure and diastolic blood pressure.

For this reason, as shown in Patent Document 2, the present inventor arranges a sensor for detecting the pulsation of the living body between the living body and the cuff band, measures the compressed pulse wave, It was proposed to measure systolic blood pressure and diastolic blood pressure from the occurrence and disappearance of appearing protrusions. Moreover, in order to make it possible to measure the compressed pulse wave more accurately, a thin metal plate and a strain gauge that is attached to one surface of the thin metal plate and detects pressure from pulsation transmitted through the thin metal plate. It was also suggested to use.
JP 2006-280485 A

  Although the compressed pulse wave has the advantage that there are fewer individual differences than the Korotkoff sound, it is still difficult to specify an accurate squeak waveform, especially during movement, muscle and bone vibration due to exercise, It was difficult to distinguish protrusions due to the influence of noise such as blood flow.

  The problem to be solved by the present invention is to provide a blood pressure measurement method capable of measuring the blood pressure both at rest and during exercise, and a blood pressure measurement device using the method, which solves the problems described above. It is. In particular, it is to provide a blood pressure measurement method and a blood pressure measurement device using the method, which can easily obtain the same result as when Korotkoff sound is accurately measured.

In order to investigate the correlation of the waveform of the measurement result obtained by the Korotkoff sound microphone and the arterial squeeze strain sensor disposed inside the cuff, the present inventor has determined the band pass filter frequency band (band pass filter frequency band) of the Korotkoff sound by the acoustic frequency analysis of the Korotkoff sound. filter), and the bandpass filter frequency band of the compressed pulse wave was analyzed by analyzing the vibrational frequency of the compressed pulse wave inside the cuff.
As a result, Korotkoff sounds are caused by arterial squeezing of the bandpass filter frequency band characteristics of the compressed pulse wave, and both spike signals (spike signals) must match in time. It was confirmed.
Thereby, from the arterial squeezing waveform (Ac) of the compressed pulse wave, it is possible to easily discriminate the same systolic blood pressure and diastolic blood pressure as measured by Korotkoff sound, and even during kinetics, as in the static state, The present inventors have found that stable measurement is possible and completed the present invention.

  In order to solve the above-mentioned problem, the invention according to claim 1 is arranged such that the strain sensor is arranged and fixed so as to be located inside the cuff and inside the center of the upper arm of the human body, and the strain is reduced while depressurizing the cuff. A compressed pulse wave measuring step for measuring a compressed pulse wave inside the cuff by a sensor, and a compressed pulse wave having a specific frequency component having a frequency of 100 Hz or less from the compressed pulse wave measured in the compressed pulse wave measuring step A blood pressure measurement comprising: a specific frequency waveform extracting step for extracting only a blood pressure; and a blood pressure value determining step for determining a maximum blood pressure value or a minimum blood pressure value of a human body based on a compressed pulse wave of the specific frequency component Is the method.

  The invention according to claim 2 is the blood pressure measurement method according to claim 1, wherein the specific frequency waveform extraction step extracts a waveform included in a frequency range of 20 to 70 Hz.

  According to a third aspect of the present invention, in the blood pressure measurement method according to the first or second aspect, in the blood pressure value determining step, based on the arterial squeezing waveform (Ac) of the compressed pulse wave of the specific frequency component, It is characterized by determining a hypertension value or a minimum blood pressure value.

  According to a fourth aspect of the present invention, in the blood pressure measurement method according to the third aspect, in the blood pressure value determining step, the arterial squeezing waveform (Ac) is converted into a compressed pulse wave of a specific frequency component or the specific frequency component. The compressed pulse wave is identified based on at least one of differential waveforms obtained by first-order or second-order differentiation.

  The invention according to claim 5 is the blood pressure measurement method according to claim 3 or 4, wherein the first detected arterial squeezing waveform is the first arterial squeezing waveform, and the cuff at the time of the first arterial squeezing waveform is used. An intermediate value between the pressure and the cuff pressure corresponding to the pulse wave immediately before the first arterial squeezing waveform is determined as the maximum blood pressure value.

  The invention according to claim 6 is the blood pressure measurement method according to claim 3 or 4, wherein the last detected arterial squeezing waveform is the final arterial squeezing waveform, and the cuff pressure at the time of the final arterial squeezing waveform is The intermediate value of the cuff pressure corresponding to the pulse wave next to the final arterial squeezing waveform is determined as the minimum blood pressure value.

  A seventh aspect of the present invention is a blood pressure measurement device using the blood pressure measurement method according to any one of the first to sixth aspects.

By extracting only the compressed pulse wave having a specific frequency component having a frequency of 100 Hz or less from the compressed pulse wave inside the cuff, the arterial squeezing waveform of the compressed pulse wave with very little noise is obtained. By determining the maximum blood pressure value or minimum blood pressure value of the human body based on the compressed pulse wave of this specific frequency component, the same maximum blood pressure value or minimum blood pressure value as measured using the Korotkoff sound can be obtained. It becomes possible to obtain blood.
Moreover, in the blood pressure measurement method of the present invention, dynamic blood pressure measurement, which was impossible with Korotkoff sound measurement, can be accurately performed as in the static state.

  According to the invention according to claim 2, the specific frequency waveform extraction step extracts a waveform included in the frequency range of 20 to 70 Hz, so that the arterial squeezing waveform in which the Korotkoff sound and the decay length match among the compressed pulse waves can be specified. It becomes possible. That is, the vibration source of the compressed pulse wave corresponding to the Korotkoff sound is assumed to be in the stagnation of the blood vessel, and by specifying that the band pass filter frequency band of the compressed pulse wave is in the frequency range of 20 to 70 Hz. It effectively eliminates most of the noise generated in the body other than the itch of the blood vessel, such as vibration of bones and muscles during exercise, blood flow noise, etc. Blood pressure can be measured at

  According to the invention of claim 3, in the blood pressure value determining step, measurement is performed with Korotkoff sound in order to determine the highest blood pressure value or the lowest blood pressure value of the human body based on the arterial squeezing waveform (Ac) of the compressed pulse wave of the specific frequency component. As in the case of the above, the maximum blood pressure and the minimum blood pressure can be easily discriminated. In addition, the measurement of the systolic blood pressure and the diastolic blood pressure during kinetics, which was difficult with the measurement method using the Korotkoff sound, can be accurately measured as in the static state.

  According to the invention of claim 4, in the blood pressure value determining step, the arterial squeezing waveform (Ac) is subjected to first- or second-order differentiation of the compressed pulse wave of the specific frequency component or the compressed pulse wave of the specific frequency component. In order to identify based on at least one of the obtained differential waveforms, an arterial squeezing waveform (Ac) which is a compressed pulse wave corresponding to the Korotkoff sound, in particular, a spike signal in the bandpass filter frequency band in the arterial squeezing waveform is accurately obtained. It can be specified, and the maximum blood pressure value and the minimum blood pressure value can be accurately measured. In particular, the differential waveform of the compressed pulse wave can make sharp fluctuations such as an arterial squeezing waveform manifest, and by using the differential waveform, a more accurate arterial squeezing waveform can be measured.

  According to the invention of claim 5, the first detected arterial squeezing waveform is the first arterial squeezing waveform, the cuff pressure at the time of the first arterial squeezing waveform, and the previous one of the first arterial squeezing waveform. Since the systolic blood pressure value is determined based on the cuff pressure corresponding to the pulse wave, blood pressure measurement that matches the systolic blood pressure value measured using the Korotkoff sound can be performed.

  According to the invention of claim 6, the last detected arterial squeezing waveform is the final arterial squeezing waveform, and corresponds to the cuff pressure at the time of the final arterial squeezing waveform and the next pulse wave of the final arterial squeezing waveform. Since the minimum blood pressure value is determined based on the cuff pressure, blood pressure measurement that matches the minimum blood pressure value when measured using Korotkoff sounds is possible.

  The invention according to claim 7 is a blood pressure measurement device using the blood pressure measurement method according to any one of claims 1 to 5, so that the blood pressure has the convenience of the blood pressure measurement method according to claims 1 to 5 described above. A measuring device can be provided.

Hereinafter, the present invention will be described in detail using preferred examples.
FIG. 1 is a flowchart showing an outline of a blood pressure measurement method according to the present invention.
In the blood pressure measurement method according to the present invention, first, the pulse wave to be compressed is measured while continuously changing the pressure for compressing the artery of the living body. Specifically, the strain sensor is arranged and fixed so that it is located inside the cuff and inside the center of the upper arm of the human body, and the pressure pulse inside the cuff is generated by the strain sensor while reducing the pressure after the cuff is pressurized. measure. In the present invention, the process of measuring such a compressed pulse wave is referred to as a compressed pulse wave measurement process (A).

Next, in order to identify the arterial squeezing waveform of the compressed pulse wave corresponding to the Korotkoff sound from the compressed pulse wave measured in the compressed pulse wave measurement step, a band pass filter frequency band of the compressed pulse wave is extracted. . Specifically, only the compressed pulse wave having a specific frequency component having a frequency of 100 Hz or less is extracted (specific frequency waveform extracting step (B)). Furthermore, based on the compressed pulse wave of the specific frequency component in the specific frequency waveform extraction step (B), the maximum blood pressure value or the minimum blood pressure value of the human body is determined (blood pressure value determination step (C)).
Thus, the blood pressure measurement method of the present invention includes a pressure pulse wave measurement step (A), a specific frequency waveform extraction step (B), and a blood pressure value determination step (C). It is.

  The measurement of the compressed pulse wave in the compressed pulse wave measurement step (A) is performed by a strain sensor disposed between the cuff serving as the compression means and the human body. As the strain sensor, the strain gauge disclosed in Patent Document 2 described above can be suitably used. In addition, by using a strain gauge, it is possible to eliminate the influence of noise sound outside the living body, and to detect vibration propagating through the living body, particularly vibration related to stagnation of blood vessels, more accurately.

The specific frequency waveform extraction step (B) can be said to be a step of specifying the bandpass filter frequency band of the compressed pulse wave.
The “bandpass filter frequency band” in the present invention means a waveform obtained by extracting a frequency component resulting from the arterial distortion waveform of each waveform, and for Korotkoff sounds, as a result of performing an acoustic frequency analysis, 500 Hz or less, In particular, a bandpass filter frequency band exists in the range of 50 to 450 Hz (50 to 270 Hz, 270 to 450 Hz).
Further, as a result of performing a vibrational frequency analysis on the compressed pulse wave, a band-pass filter frequency band exists in a range of 100 Hz or less, more preferably 20 to 70 Hz.

  The Korotkoff sound waveform is classified into five from the Swan (I) point to the (V) point according to the change in vibration intensity over time in the process of the cuff pressure continuously changing from high pressure to low pressure. Becomes the Swan (I) point, and the minimum blood pressure becomes the Swan (IV) point.

FIGS. 2 to 4 show Korotokoff sound and oppressed pulse wave (Oppressed) for Swan (I) to (V) and part of the pulse wave before and after the cuff pressure is changed from high pressure to low pressure. The frequency spectrum of (Pulse Wave) is shown. In particular, FIG. 2 shows the pulse wave (Swan (0)) immediately before Swan (I), FIG. 3 shows the state of Swan (I), and FIG. 4 shows the state of Swan (IV).
The thick line in each graph shows the measured waveform at each stage, but the thin line in FIGS. 3 and 4 shows the waveform in FIG. 2, that is, the background (noise) that is not the arterial strain waveform. .

  FIG. 5 characterizes the Korotkoff sounds obtained from the results of measuring and analyzing the frequency spectrum at each stage of Swan (0) to Swan (V) as shown in FIGS. The frequency distribution range and the frequency distribution range that characterizes the arterial squeezing waveform of the compressed pulse wave are shown. In particular, it shows for reference how the frequency distribution range of each waveform changes from the point Swan (0) (the previous stage of Swan (I)) to the point (V). . It is understood that the Korotkoff sound distribution is distributed at each point of the Swan, and at the point (III), sounds of frequencies in the four frequency regions are generated in combination. For this reason, it is easily understood that measuring blood pressure using the Korotkoff sound auscultation method requires skill.

  On the other hand, the compressed pulse wave changes in a frequency range of 100 Hz or less. By measuring the compressed pulse wave of this specific frequency component, from the Swan (I) point corresponding to the Korotkoff sound (V) In particular, it is possible to accurately discriminate and measure (0) point, (I) point, (IV) point, and (V) point.

Next, the blood pressure value determination step in the blood pressure measurement method of the present invention will be described.
An important point in determining the systolic blood pressure and diastolic blood pressure is to determine the squeezing (waveform) of the artery that is the cause of Korotkoff sound from the compressed pulse wave, especially the bandpass filter frequency band of the compressed pulse wave. How to identify.

FIGS. 6-8 show charts of arbitrary resting cases recorded in the depressurization process after cuff pressurization, and display the next seven channels.
(1) Ac: compression pulse wave (2) Acl: all frequency components of 20 to 70 Hz extracted from the compression pulse wave (3) Ach: high frequency components of 45 to 65 Hz extracted from the compression pulse wave Things (4) Ks: Korotkoff sounds (5) Ksl: All frequency components of 50 to 270 Hz extracted from Korotkoff sounds (6) Ksh: High frequency components of 270 to 500 Hz extracted from Korotkoff sounds (7) Cp : Cuff pressure (Pressure value is indicated by numerical value mmHg at the top of the graph)

  In FIG. 6, when the cuff pressure is 139 mmHg, the first pointed concave, convex spike, the so-called arteries, is shown in Ac (first stage), Accl (second stage) and Ach (sixth stage). A distortion waveform appears. The first sharp spikes appear in Ks (third stage), Ksl (fourth stage), and Ksh (fifth stage) with a delay of about 80 ms.

It can be understood from the transition of the waveforms of FIGS. 6 to 8 that the fluctuations of the arterial squeezing waveform (Ac) and the Korotkoff sound (Ks) of the compressed pulse wave completely coincide.
As shown in FIG. 6, the first detected blood pressure value (Ps) corresponds to the first arterial squeezing waveform (Ac), which corresponds to the first arterial squeezing waveform (Ac). The cuff pressure 139 mmHg at the time of the first arterial squeezing waveform and the cuff pressure 145 mmHg corresponding to the pulse wave immediately before the first arterial squeezing waveform (corresponding to preAcI, Swan (0)). .
Theoretically, an intermediate value between the two can be adopted, and in this case, 141 mmHg.

As shown in FIG. 8, the last detected blood pressure value (Pd) is the final arterial squeezing waveform (corresponding to lastAcIV, Swan (IV)) of the arterial squeezing waveform (Ac). It is determined by the cuff pressure of 93 mmHg at the time of the arterial squeezing waveform and the cuff pressure of 90 mmHg corresponding to the next pulse wave of the final arterial squeezing waveform (corresponding to postAcIV, Swan (V)).
As for the minimum blood pressure value, as in the maximum blood pressure value, an intermediate value between the two can theoretically be adopted. In this case, it is determined to be 91 mmHg.

  As shown in the waveform transition of FIG. 6 or FIG. 8, the arterial squeezing waveform is already observed in the compressed pulse wave (Ac) before and after the Korotkoff sound (Ks) is measured. It is understood that the pulse wave can identify the arterial squeezing waveform with higher sensitivity than the Korotkoff sound. In addition, the waveform (Acl) obtained by extracting the frequency component of 20 to 70 Hz, which is the specific frequency component of the compressed pulse wave (Ac), is a bar vein squeak waveform as a whole efficiently from the start to the end of the arterial squeak waveform. Has been extracted. In addition, the waveform (Ach) obtained by extracting the frequency component of 45 to 65 Hz from the compressed pulse wave can be observed in the same manner as the arterial squeezing waveform in the range in which the Korotkoff sound is observed. In the range II) to (III) or (IV), it is easily understood that Ach can observe the arterial squeezing waveform more characteristicly than the Acl waveform.

Next, a method for identifying an arterial squeezing waveform based on a differential waveform obtained by first-order or second-order differentiation of the arterial squeezing waveform (Ac) bandpass filter frequency band in the blood pressure value determining step will be described.
FIGS. 9 to 11 show the compressed pulse wave (Ac) in the first stage and the waveform (Acl) obtained by extracting a frequency component of 20 to 70 Hz from the compressed pulse wave (Ac) in the fourth stage when resting. is doing. The second stage shows the first-order differential pulse wave (Acldf1) obtained by first-derivative of Acl, and the third stage shows the second-order differential pulse wave (Acldf2) obtained by second-order differentiation of Acl.

  The reason for differentiating Acl in this way is that the characteristics of a pointed concave and convex spike, which is an arterial distorted pulse wave, have been made clearer, and even when a recording failure waveform due to an individual or noise such as exercise load is mixed. Thus, the arterial strain waveform can be specified accurately.

  The five types of rectangular waveforms in the fifth to ninth stages of the graphs shown in FIGS. 9 to 11 indicate logic for specifying the arterial strain pulse wave. In particular, the fifth to seventh stages displayed as “logic construction” provide information necessary for configuring the logic. Specifically, the fifth row shows the result of logical determination as to whether or not the amplitude value of the waveform (Acl) obtained by extracting the specific frequency component of the compressed pulse wave (Ac) exceeds a predetermined level. The sixth row shows the result of logical determination as to whether or not the amplitude value of the primary differential pulse wave (Acldf1) exceeds a predetermined level. The seventh row shows the result of logical determination as to whether or not the amplitude value of the second-order differential pulse wave (Acldf2) exceeds a predetermined level.

  The 8th to 9th stages show logical diagnosis results for specifying the maximum blood pressure value (Ps) and the minimum blood pressure value (Pd). These indicate the logically determined results based on the information displayed in the 5th to 7th stage logic construction. In other words, the frequency distribution intensity integral of the Acl differential waveform by Fourier analysis was analyzed in the same way, and it was proved that it was stochastically different from the integral of the Swan (0) point and Swan (IV) point. Sometimes a logic diagnosis is made.

The cuff pressure at the time of the first arterial squeezing waveform is diagnosed as 139 mmHg based on the result of the logic diagnosis (8th to 9th stages) in FIG. It is understood that the pressure is diagnosed as 93 mmHg.
Thus, by using the blood pressure measurement method of the present invention, it is possible to accurately logically diagnose the maximum or minimum blood pressure value.

Next, in order to measure the blood pressure value during kinetics, the subject made a sprinting motion from walking (3, 5, 7, and 9 (km / h) per hour) on an endless belt (treadmill) device, and the compressed pulse wave Was measured. Based on the measured compressed pulse wave, a logical diagnosis was performed in the same manner as shown in FIGS. 12 to 13 show measurement results and logic diagnosis results when a load of 7 (km / h) is applied per hour. Thereby, it is understood that the cuff pressure at the time of the first arterial squeezing waveform is diagnosed as 163 mmHg, and the cuff pressure at the time of the final arterial squeezing waveform is diagnosed as 100 mmHg. During the decompression, the cuff pressure fluctuates up and down due to the pulsating flow and falls. A cuff pressure behavior during this time is memorized in time series, and a software program that reads the spike signal cuff pressure is built in.
From this measurement result, it is determined that the maximum blood pressure value during the dynamics of 7 km / h is 174 mmHg and the minimum blood pressure value is 97 mmHg.

  Next, measured values (Ks diagnosis) of systolic blood pressure value (Ps) and diastolic blood pressure value (Pd) by resting Korotkoff sound (Ks), systolic blood pressure value (Ps) and diastolic blood pressure value by compressed pulse wave (Ac) The measurement results of (Pd), (Ac diagnosis), and the measurement results (logic diagnosis) of the systolic blood pressure value (Ps) and the diastolic blood pressure value (Pd) by the above logic (logic) diagnosis are compared with each other, and the identity Evaluated.

The total number of test subjects was 146 cases of ages 20 to 70 years old. Among them, 60 cases at rest and 86 cases at exercise were used.
At rest, FIG. 14 shows a comparison result between the Ks diagnosis and the Ac diagnosis, FIG. 15 shows a comparison result between the Ks diagnosis and the logic diagnosis, and FIG. 16 shows a comparison result between the logic diagnosis and the Ac diagnosis. .

  The correlation coefficient r of each comparison result combining the systolic blood pressure value (Ps) and the diastolic blood pressure value (Pd) is r = 0.994 in FIG. 14, r = 0.991 in FIG. 15, and r = 0.99 in FIG. It was 0.993, and Ks (Korotkoff sound), Ac (compressed pulse wave, in particular, arterial squeezing waveform), and logic diagnosis (automatic diagnosis) were almost completely in agreement.

  In addition, regarding exercise load, the results of 86 subjects who performed the above-described walking using the endless belt device (treadmill) to sprinting exercise (speeds 3, 5, 7, and 9 (km / h)). FIG. 17 shows a comparison result between the logic diagnosis and the Ac diagnosis.

  The correlation coefficient r of the comparison result obtained by combining the maximum blood pressure value (Ps) and the minimum blood pressure value (Pd) is r = 0.995, and the ac (compressed) is applied in the exercise load by the endless belt over 3 to 9 km / h. The pulse wave (especially arterial squeezing waveform) and the logic diagnosis (automatic diagnosis) were almost perfectly matched.

Next, a blood pressure measurement device using the blood pressure measurement method of the present invention will be described.
FIG. 18 is a block diagram showing an outline of the blood pressure measurement device, and a waveform signal a of a compressed pulse wave detected by the pressure sensor 1 that is a strain sensor is input to the control circuit 4.

The control circuit 4 drives and controls the pressure increasing / decreasing means 3 such as a pump connected to the cuff band 2 and introduces or leads air d into the cuff band 2 to change the pressure of the cuff band 2.
A sensor for detecting the pressure in the cuff band 2 is separately provided, and a signal b obtained by measuring the pressure in the cuff band 2 is input to the control circuit 4.

The pressure sensor 1 is disposed inside the upper arm center inside the cuff belt 2 wound around the upper arm, and observes vibrations of living body blood vessels that are squeezed by compression.
The waveform from the pressure sensor 1 is a compressed pulse wave, and the control circuit 4 extracts a specific frequency component having a frequency of 100 Hz or less (or a range of 20 to 70 Hz) from the compressed pulse wave.

  From the control circuit, a waveform of the extracted frequency component (a bandpass filter frequency band of the compressed pulse wave) is output. Further, the control circuit determines a predetermined blood pressure value based on the bandpass filter frequency band of the compressed pulse wave using the determination method of the maximum blood pressure value or the minimum blood pressure value in the above-described blood pressure value determination step. In determining the blood pressure value, a signal b indicating a necessary cuff pressure is acquired.

  From the control circuit 4, various data e such as raw data of the pressure sensor 1, pressure measurement data of the cuff band 2, further, a band pass filter frequency band of the compressed pulse wave, and frequency distribution data obtained by frequency analysis can be output. The data can be output to display output means such as a display or a printer, or transmitted to another computer or the like for use in various analyses. It is also possible to automatically determine the systolic blood pressure value or the diastolic blood pressure value in the control circuit 4 and output only the numerical value as the output signal e.

  As described above, according to the present invention, it is possible to provide a blood pressure measurement method capable of measuring blood pressure both at rest and during exercise, and a blood pressure measurement device using the method. In particular, it is possible to provide a blood pressure measurement method and a blood pressure measurement device using the method that can easily obtain the same result as when Korotkoff sound is accurately measured.

The flowchart of the blood-pressure measuring method of this invention is shown. It is a graph which shows the frequency spectrum of the Korotkoff sound (Korotokov sound) and the oppressed pulse wave (Oppressed Pulse Wave) in Swan (0). It is a graph which shows the frequency spectrum of the Korotkoff sound in Swan (I) and the compressed pulse wave. It is a graph which shows the frequency spectrum of the Korotkoff sound in Swan (IV) and the compressed pulse wave. It is a figure which shows the spectrum analysis range of a Korotkoff sound and a to-be-compressed pulse wave. It is a graph (the 1) which shows the change in the decompression process after the cuff pressurization of the to-be-compressed pulse wave (Ac) and the Korotkoff sound (Ks). It is a graph (the 2) which shows the change in the decompression process after the cuff pressurization of the to-be-compressed pulse wave (Ac) and the Korotkoff sound (Ks). It is a graph (the 3) which shows the change in the decompression process after the cuff pressurization of the to-be-compressed pulse wave (Ac) and the Korotkoff sound (Ks). It is a graph (the 1) which shows a to-be-compressed pulse wave (Ac) and its differential waveform, and logic (logic) diagnosis. It is a graph (the 2) which shows a to-be-compressed pulse wave (Ac) and its differential waveform, and logic (logic) diagnosis. It is a graph (the 3) which shows a to-be-compressed pulse wave (Ac) and its differential waveform, and logic (logic) diagnosis. It is the graph (the 1) which shows the to-be-compressed pulse wave (Ac) in dynamics, its differential waveform, and logic (logic) diagnosis. It is the graph (the 2) which shows the to-be-compressed pulse wave (Ac) in dynamics, its differential waveform, and logic (logic) diagnosis. It is a graph which shows the comparison result of Ks diagnosis and Ac diagnosis at the time of rest. It is a graph which shows the comparison result of Ks diagnosis and logic diagnosis at the time of rest. It is a graph which shows the comparison result of a logic diagnosis and an Ac diagnosis at the time of rest. It is a graph which shows the comparison result of logic diagnosis and Ac diagnosis in dynamics. It is a block diagram which shows the outline of the blood-pressure measuring apparatus of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Pressure sensor 2 Cuff belt 3 Pressure-reducing means 4 Control circuit 5 Display output means

Claims (7)

A strain sensor is placed and fixed so that it is located inside the cuff and inside the upper arm center of the human body, and the pressure pulse measured by the strain sensor while measuring the pressure pulse wave inside the cuff while depressurizing the cuff. Wave measurement process,
A specific frequency waveform extracting step of extracting only the compressed pulse wave of a specific frequency component having a frequency of 100 Hz or less from the compressed pulse wave measured in the compressed pulse wave measurement step;
And a blood pressure value determining step for determining a maximum blood pressure value or a minimum blood pressure value of the human body based on the compressed pulse wave of the specific frequency component.   2. The blood pressure measurement method according to claim 1, wherein the specific frequency waveform extraction step extracts a waveform included in a frequency range of 20 to 70 Hz.   3. The blood pressure measurement method according to claim 1, wherein, in the blood pressure value determination step, a maximum blood pressure value or a minimum blood pressure value of the human body is determined based on an arterial squeezing waveform (Ac) of the compressed pulse wave of the specific frequency component. A blood pressure measurement method characterized by:   4. The blood pressure measurement method according to claim 3, wherein in the blood pressure value determination step, the arterial squeezing waveform (Ac) is a primary frequency or a compressed pulse wave of a specific frequency component, or a compressed pulse wave of the specific frequency component is primary or A blood pressure measurement method characterized by identifying based on at least one of differential waveforms obtained by secondary differentiation.   5. The blood pressure measurement method according to claim 3 or 4, wherein the first detected squeezing waveform of the arterial squeezing waveform is a first arterial squeezing waveform, and the cuff pressure at the time of the first arterial squeezing waveform and the first arterial squeezing A blood pressure measurement method, wherein a maximum blood pressure value is determined based on a cuff pressure corresponding to a pulse wave immediately before the waveform.   5. The blood pressure measurement method according to claim 3 or 4, wherein the last detected squeezing waveform of the arterial squeezing waveform is a final arterial squeezing waveform, the cuff pressure at the time of the final arterial squeezing waveform, and the next of the final arterial squeezing waveform A blood pressure measurement method, wherein a minimum blood pressure value is determined based on a cuff pressure corresponding to the pulse wave.   A blood pressure measurement device using the blood pressure measurement method according to claim 1.

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