JP5049097B2 - Pulse wave detection compression band, and automatic blood pressure measurement device, blood vessel flexibility measurement device, and pulse wave propagation velocity measurement device including the same. - Google Patents

Description

  The present invention relates to a compression band wound around a compression site to detect a pulse wave generated from an artery in the compression site that is a limb of a living body such as an arm or an ankle, and an automatic equipped with the compression zone The present invention relates to a blood pressure measuring device, a blood vessel flexibility measuring device, and a pulse wave velocity measuring device.

  Biological circulatory information such as the blood pressure value, pulse wave velocity, and arterial flexibility (compliance) of the living body is measured based on the pulse wave generated from the living artery. The pulse wave generated from the artery of the living body is easily detected as pressure vibration in the compression band wound around the pressed portion of the living body. However, the inflatable bag provided in this compression band (cuff) requires a sufficiently large compression width for the diameter of the area to be compressed and has a relatively large capacity, so it responds to changes in arterial volume. The pulse wave, which is the pressure vibration generated in this way, tends to be a weak signal, and the compression pressure at the end in the width direction of the compression band is attenuated with respect to the compression site. For example, the effective width is a pulse wave obtained in a non-uniform state of 80% or less, which causes measurement errors.

On the other hand, as shown in Patent Document 1, a small-capacity detection inflation bag is provided inside the main inflation bag with respect to the main inflation bag in order to clearly detect a change in arterial volume. A two-layered compression band in which a shielding plate is provided between the expansion bag for main use and the main expansion bag has been proposed. According to this, pressurization by the main inflation bag is performed directly to the pressed portion and indirectly through the detection inflation bag, and when detecting the pulse wave, the main inflation bag and the detection inflation bag By blocking the air diameter between them or applying resistance, the pressure fluctuation is made independent, and a pulse wave, which is pressure vibration generated in the detection inflation bag due to the arterial volume fluctuation, is detected. At this time, since the detection expansion bag is shielded from the main expansion bag by the shielding plate and has a relatively small volume, a pulse wave, which is pressure vibration in the detection expansion bag, can be obtained to some extent accurately. become able to.
Japanese Patent Laid-Open No. 05-269089

  However, according to the conventional two-layer compression band shown in Patent Document 1, the pressure of the main inflation bag is not properly applied to the artery because the detection inflation bag is located on the skin side of the living body. Therefore, there was an inconvenience that it was difficult to obtain an accurate pulse wave.

  An object of the present invention is to provide a pulse wave detection compression band capable of appropriately applying a compression pressure to an artery in a compressed portion of a living body and obtaining an accurate pulse wave, and an automatic blood pressure equipped with the pressure wave detection band. To provide a measuring device, a blood vessel flexibility measuring device, and a pulse wave velocity measuring device.

In order to achieve this object, the invention according to claim 1 is: (a) a pulse wave detection compression band that is wound around a compressed portion of a living body in order to detect a pulse wave generated from an artery of the living body; (B) a pair of upstream inflatable bag and downstream inflatable bag made of a flexible sheet positioned at a predetermined interval in the longitudinal direction of the compressed portion; and (c) in the longitudinal direction of the compressed portion. A detection inflatable bag disposed between the pair of upstream inflatable bags and the downstream inflatable bag so as to be continuous and having an air chamber independent of the pair of upstream inflatable bags and the downstream inflatable bag; (d) Detecting a pressure fluctuation in the detection inflation bag as the pulse wave in a state where the compressed portion of the living body is compressed with the same pressure by the upstream inflation bag, the detection inflation bag, and the downstream inflation bag. to make it in, (e) wherein the detection in the longitudinal direction of the compression site A pair of folding grooves made of flexible sheets folded in directions approaching each other are formed at both ends of the expansion bag, and (f) the detection expansion bag of the upstream expansion bag and the downstream expansion bag The adjacent side end portions on the adjacent sides are inserted into the pair of folding grooves .

A pulse wave detection compression band according to a second aspect of the present invention is the invention according to the first aspect, wherein at least one of the opposed groove side surfaces of the pair of folding grooves of the detection inflating bag is inserted into the folding groove. Bending in the width direction of the pressure detection band for pulse wave detection rather than the bending rigidity in the longitudinal direction of the compression band for pulse wave detection between the upstream expansion bag and the adjacent side end of the downstream expansion bag A long shielding member having high rigidity and anisotropic rigidity is interposed.

According to a third aspect of the present invention, there is provided the compression band for pulse wave detection according to the second aspect of the present invention, wherein the longitudinal shielding member is a plurality of flexible hollows parallel to the longitudinal direction of the pressed portion. The tube is configured by being arranged in a row in the circumferential direction of the pressed portion in a state of being parallel to each other.

An automatic blood pressure measurement device according to a fourth aspect of the present invention comprises: (a) the pulse wave detection compression band according to any one of the first to third aspects, and (b) in the inflatable bag for detection. A pressure sensor for detecting the pressure of the pair of upstream inflatable bags and the downstream inflatable bag and the inflatable bag for detection to pressurize the artery in the compressed site by increasing the pressure in a mutually connected state. Pressure control means for compressing and continuously changing the compression pressure, and (d) a pulse wave which is a pressure vibration component of the compression pressure detected by the pressure sensor in the process of changing the compression pressure by the pressure control means And oscillometric blood pressure measuring means for determining the blood pressure value of the living body based on the change of the pulse wave.

According to a fifth aspect of the present invention, there is provided the blood vessel flexibility measuring device according to the fifth aspect , comprising: (a) the automatic blood pressure measuring device according to the fourth aspect , and (b) a pressure vibration component of the compression pressure detected by the pressure sensor. And an arterial compliance calculating means for calculating arterial compliance indicating the flexibility of the artery based on the amplitude value of the pulse wave and the blood pressure value measured by the automatic blood pressure measuring device.

Further, in the blood vessel flexibility measuring device according to the invention of claim 6 , the arterial compliance calculating means changes the amplitude value of the pulse wave from the pressure unit to the volume unit from the relationship of the pressure change with respect to the volume change of the detection inflation bag. A cuff compliance calculating means for calculating a cuff compliance for conversion, and the pressure difference between the amplitude value of the pulse wave converted into the volume unit and the maximum blood pressure value and the minimum blood pressure value detected by the automatic blood pressure measuring device; Based on the above, an arterial compliance indicating the flexibility of the artery is calculated.

According to a seventh aspect of the present invention, there is provided the blood vessel flexibility measuring device according to the present invention, wherein: (a) a constant volume pulse wave that applies a predetermined volume of gas having a size corresponding to the pulsation of the artery into the detection inflation bag; And (b) the arterial compliance calculating means includes a volume value of a constant volume of gas added to the detection inflation bag by the constant volume pulse wave generator, and the fixed volume of gas is used for the detection. It is characterized in that a relationship with a pressure increase value in the detection expansion bag detected by the pressure sensor when applied to the expansion bag is obtained in advance.

According to an eighth aspect of the present invention, there is provided a pulse wave velocity measuring device according to the invention, comprising: (a) the pulse wave detection compression band according to any one of the first to third aspects; and (b) the upstream expansion. A first pressure sensor for detecting the pressure in the bag; (c) a third pressure sensor for detecting the pressure in the downstream expansion bag; and (d) the living body in the upstream expansion bag and the downstream expansion bag . Pulse wave propagation time from the pulse wave detected by the first pressure sensor to the pulse wave detected by the third pressure sensor in a state where the gas is filled at a pressure lower than the lowest blood pressure value, and the upstream side And a pulse wave velocity measuring means for calculating the pulse wave velocity in the artery based on the center-to-center distance between the inflation bag and the downstream inflation bag .

The pulse wave detection compression band of the invention according to claim 1 is a pair of an upstream expansion bag and a downstream expansion bag made of a flexible sheet positioned at a predetermined interval in the longitudinal direction of the pressed portion, Detection that has an air chamber that is arranged between the pair of upstream inflation bags and the downstream inflation bag so as to be continuous in the longitudinal direction of the compressed portion, and is independent of the pair of upstream inflation bags and the downstream inflation bag. Pressure fluctuation in the detection inflation bag in a state where the compressed portion of the living body is compressed with the same pressure by the upstream inflation bag, the detection inflation bag, and the downstream inflation bag. This is detected as the pulse wave. For this reason, while applying compression pressure with an even pressure distribution from the upstream inflation bag, the detection inflation bag, and the downstream inflation bag that are continuous in the longitudinal direction of the compression site to the artery in the compression site of the living body, A pulse wave is obtained. Furthermore, a pair of folding grooves made of a flexible sheet folded in a direction approaching each other are formed at both ends of the detection expansion bag in the longitudinal direction of the pressed portion, and the upstream expansion bag and the downstream Since the adjacent side end of the side expansion bag adjacent to the detection expansion bag is inserted into the pair of folding grooves, both ends of the detection expansion bag, the upstream expansion bag, and the downstream expansion Since the adjacent side end portion of the bag is overlapped in the radial direction of the compressed part, the bag is also against the compressed part in the vicinity of the boundary between the detection expansion bag, the upstream expansion bag, and the downstream expansion bag. A uniform pressure distribution is obtained.

According to the pulse wave detection compression band of the invention according to claim 2 , at least one of the opposing groove side surfaces of the pair of folding grooves of the detection inflation bag and the upstream inserted in the folding groove Between the side expansion bag and the adjacent side end portion of the downstream expansion bag, a rigidity anisotropy having a higher bending rigidity in the width direction of the compression band than the bending rigidity in the longitudinal direction of the compression band for pulse wave detection. In particular, the low-frequency pressure vibration noise shielding action from the upstream inflatable bag and the downstream inflatable bag to the detection inflatable bag can be suitably obtained and the relatively low An accurate pulse wave that is hardly affected by pressure vibration noise of the frequency can be obtained.

According to the pulse wave detection compression band of the invention of claim 3 , the longitudinal shielding member is in a state in which a plurality of flexible hollow tubes parallel to the longitudinal direction of the pressed part are parallel to each other. Therefore, the low-frequency pressure vibration noise is shielded from the upstream inflatable bag and the downstream inflatable bag to the detecting inflatable bag. Can be obtained more suitably, and a more accurate pulse wave that is not easily affected by pressure vibration noise of a relatively low frequency can be obtained.

According to the automatic blood pressure measurement device of the invention of claim 4 , the detection inflation bag, the pressure sensor for detecting the pressure in the detection inflation bag, the pair of upstream inflation bags and the downstream inflation A pressure control unit that pressurizes an artery in the compressed portion by pressurizing the bag and the inflatable bag for detection in a state where they are in communication with each other, and a pressure control unit that continuously changes the compression pressure; An oscillometric blood pressure measurement that extracts a pulse wave, which is a pressure vibration component of the compression pressure detected by the pressure sensor in the process of changing the pressure, and determines a blood pressure value of the living body based on the change of the pulse wave. Therefore, a highly accurate blood pressure value can be obtained based on an accurate pulse wave obtained from the detection inflation bag.

According to the vascular flexibility measuring device of the invention according to claim 5 , the amplitude value of the pulse wave that is the pressure vibration component of the compression pressure detected by the pressure sensor and the blood pressure value measured by the automatic blood pressure measuring device. And an arterial compliance measuring means for calculating arterial compliance indicating the degree of arterial flexibility based on the accuracy of the pulse wave obtained from the detection inflation bag and the accuracy of the calculated pulse wave. Based on the high blood pressure value, a high degree of arterial flexibility can be obtained.

According to the blood vessel flexibility measuring device of the invention according to claim 6 , the arterial compliance calculating means calculates the amplitude value of the pulse wave from the pressure unit to the volume from the relationship of the pressure change with respect to the volume change of the detection inflation bag. A cuff compliance calculating means for calculating a cuff compliance for conversion into a unit, and the pressure between the amplitude value of the pulse wave converted into the volume unit and the maximum blood pressure value and the minimum blood pressure value detected by the automatic blood pressure measurement device Since the arterial compliance indicating the arterial flexibility is calculated based on the difference, more accurate arterial flexibility can be obtained.

According to the vascular flexibility measuring device of the invention according to claim 7 , constant volume pulse wave generation for adding a predetermined volume of gas having a size corresponding to the pulsation of the artery into the inflatable bag for detection. The cuff compliance calculating means includes a volume value of a constant volume of gas added to the detection inflation bag by the constant volume pulse wave generator, and the constant volume of gas is contained in the detection inflation bag. Since the relationship with the pressure increase value in the detection inflatable bag detected by the pressure sensor when it is added is obtained in advance, the cuff compliance of the inflatable bag for detection is set in advance by that relationship, for example Each time a constant volume of gas is added from the constant volume pulse wave generator into the detection inflating bag in response to a constant period, pulse, or pressure change value, it is obtained sequentially.

According to the pulse wave velocity measuring device of the invention according to claim 8 , the pulse wave detection compression band, the first pressure sensor for detecting the pressure in the upstream expansion bag, and the downstream expansion bag A third pressure sensor for detecting the internal pressure, and the first pressure sensor in a state where the upstream inflation bag and the downstream inflation bag are filled with gas at a pressure lower than the minimum blood pressure value of the living body. Based on the pulse wave propagation time from the pulse wave detected by the third pressure sensor to the pulse wave detected by the third pressure sensor and the center-to-center distance between the upstream inflation bag and the downstream inflation bag. Since the pulse wave velocity measuring means for calculating the wave wave velocity is included, the local pulse wave velocity value of the artery in the compressed part of the living body can be easily obtained. Preferably, the pulse wave propagation time from the pulse wave detected by the second pressure sensor to the pulse wave detected by the third pressure sensor in a state where the inside of the detection expansion bag is exhausted is calculated. In this way, the space between the upstream expansion bag and the downstream expansion bag is sufficiently shielded, so that the detected pulse wave is accurate, and a highly accurate propagation speed is obtained.

  Hereinafter, an embodiment of the present invention will be described in detail with reference to the drawings.

  FIG. 1 shows a circulatory organ information measuring device 14 provided with an upper arm compression band 12 which is an example of a pulse wave detection compression band of the present invention wound around a living body limb such as the upper arm 10 which is a pressed part. . This circulatory organ information measuring device 14 measures a pressure pulse wave APW generated from an artery 16 in a living limb 10, a blood pressure value BP of the living body, an arterial flexibility (arterial compliance) K, and a pulse wave propagation velocity PWV. Therefore, it functions as a pressure pulse wave detection device, an automatic blood pressure measurement device, a blood vessel (arterial) flexibility measurement device, and a pulse wave propagation velocity measurement device.

  FIG. 2 is a partially cutaway view showing the outer peripheral surface of the compression band 12, and FIG. 3 is a view showing the inner peripheral surface of the compression band 12. As shown in FIG. 2 and FIG. 3, the compression band 12 includes a belt-shaped outer bag 20 composed of an outer peripheral side nonwoven fabric 20a and an inner peripheral side nonwoven fabric 20b made of synthetic resin fibers, the back surface of which is laminated with a synthetic resin such as PVC, An upstream inflatable bag 22, a detection inflatable bag 24, and a downstream inflatable bag 26, which are sequentially accommodated in the width direction in the belt-like outer bag 20 and are made of a flexible sheet such as a soft polyvinyl chloride sheet, for example, are provided. The raised pile 30 attached to the end of the inner peripheral nonwoven fabric 20 is detachably attached to the hook and loop fastener 28 attached to the end of the outer peripheral side nonwoven fabric 20a, so that the upper arm 10 is detachably attached. It is like that. The upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 constitute independent air chambers, and include pipe connection connectors 32, 34, and 36 on the outer peripheral surface side. The pipe connecting connectors 32, 34, and 36 are exposed to the outer peripheral surface of the compression band 12 through the outer peripheral side nonwoven fabric 20a.

  FIG. 4 is a plan view showing the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 provided in the compression band 12, and FIG. 5 is a cross-sectional view of them cut in the width direction. FIG. 6 is a perspective view showing them separately. The upstream expansion bag 22, the middle flow expansion bag 24, and the downstream expansion bag 26 each have a longitudinal shape, and the upstream expansion bag 22 and the downstream expansion bag 26 are adjacent to both sides of the detection expansion bag 24. Is arranged in. The detection expansion bag 24 is for detecting the pulse wave PW generated from the artery 16 and is in the width direction of the compression band 12 while being sandwiched between the upstream expansion bag 22 and the downstream expansion bag 26. It is arranged at the center of the.

  The detection inflatable bag 24 has side edges of a so-called gusset structure on both sides. That is, at both ends of the upper arm 10 in the longitudinal direction of the upper arm 10 for detection, a pair of folding grooves 24f and 24f made of a flexible sheet folded in a direction approaching each other so as to approach each other are formed. Each is formed. The adjacent end portions 22a and 26a of the upstream expansion bag 22 and the downstream expansion bag 26 adjacent to the detection expansion bag 24 are inserted into the pair of folding grooves 24f and 24f. It has become. Thereby, both ends of the detection expansion bag 24 and the adjacent side end portions 22a and 26a adjacent to the detection expansion bag 24 of the upstream expansion bag 22 and the downstream expansion bag 26 are overlapped with each other, that is, Because of the overlap structure, even when the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 press the upper arm 10 with equal pressure, a uniform pressure distribution is obtained even in the vicinity of the boundary. In this case, the upstream inflation bag 22 and the downstream inflation bag 26 function exclusively as a main inflation bag for compressing the upper arm 10, and the detection inflation bag 24 is a pulse that exclusively detects a pulse wave generated from the artery 16. It functions for wave detection.

  The upstream expansion bag 22 and the downstream expansion bag 26 also include end portions 22b and 26b opposite to the detection expansion bag 24 at the side edges of the so-called gusset structure. That is, the end portions 22b and 26b of the upstream side expansion bag 22 and the downstream side expansion bag 26 opposite to the detection expansion bag 24 may be folded in a direction approaching each other so as to become deeper as they approach each other. Folding grooves 22f and 26f made of a flexible sheet are respectively formed. The sheets constituting the folding grooves 22f and 26f are opposite to each other via connection sheets 38 and 40 having through holes arranged in the upstream expansion bag 22 and the downstream expansion bag 26 so as not to protrude in the width direction. It is connected to the side portion, that is, the portion on the detection expansion bag 24 side. As a result, the compression pressure on the upper arm 10 is obtained at the end portions 22b and 26b of the upstream inflatable bag 22 and the downstream inflatable bag 26 in the same manner as other portions, so that the effective compression width in the width direction of the compression band 12 is It is equivalent to the width dimension. The width direction of the compression band 12 is about 12 cm, and since the three upstream expansion bags 22, the detection expansion bag 24, and the downstream expansion bag 26 are arranged in the width direction, each is substantially The width must be about 4 cm. In order to sufficiently generate the compression function even with such a narrow width dimension, both end portions 24a and 24b of the detection inflatable bag 24 and adjacent end portions 22a and 26a of the upstream inflatable bag 22 and the downstream inflatable bag 26 are used. And end portions 22b and 26b of the upstream side expansion bag 22 and the downstream side expansion bag 26 opposite to the detection expansion bag 24 are side edges of a so-called gusset structure. It is considered to be a part.

  Ends 22a and 26a on the detection expansion bag 24 side of the upstream expansion bag 22 and the downstream expansion bag 26, and inner wall surfaces of the pair of folding grooves 24f and 24f into which they are inserted, that is, opposite groove side surfaces Between them, there are interposed longitudinal shielding members 42 having rigidity anisotropy in which the bending rigidity in the width direction of the compression band 12 is higher than the bending rigidity in the longitudinal direction of the compression band 12. In this embodiment, as shown in FIGS. 4 and 5, the outer peripheral side gap among the gaps between the end portion 22 a of the upstream inflatable bag 22 and the folding groove 24 f into which it is inserted, and the downstream side Longitudinal shielding members 42 are interposed in gaps on the outer peripheral side of the gaps between the end portions 26a of the side expansion bags 26 and the folding grooves 24f into which the side expansion bags 26 are inserted. May also be interposed. Since the outer circumferential side gap has a larger shielding effect than the inner circumferential side gap, it is sufficient to be provided at least in the outer circumferential side gap.

  The longitudinal shielding member 42 is formed in the circumferential direction of the upper arm 10, that is, in the compression state, with a plurality of resin-made flexible hollow tubes 44 parallel to the longitudinal direction of the upper arm 10, that is, the width direction of the compression band 12. The flexible hollow tubes 44 are arranged in a row in the longitudinal direction of the belt 12, and the flexible hollow tubes 44 are directly or indirectly connected to each other by molding or bonding, or indirectly through another member such as a flexible sheet such as an adhesive tape. It is comprised by connecting to. The longitudinal shielding member 42 is hung on a plurality of latching sheets 46 provided at a plurality of locations on the outer peripheral side of the end portions 22a and 26a on the detection expansion bag 24 side of the upstream expansion bag 22 and the downstream expansion bag 26. Stopped.

  FIG. 7 shows a test result showing the performance of blocking vibration from the detection expansion bag 24 to the upstream expansion bag 22 and the downstream expansion bag 26. FIG. 8 shows the detection expansion bag 24 and the downstream from the upstream expansion bag 22. The test result showing the isolation | blocking performance of the vibration to the side expansion bag 26 is shown. Since the main frequency component of the pulse wave generated from the artery 16 that is the detection target of the detection inflation bag 24 is about 6 Hz, the horizontal axis of FIGS. 7 and 8 is a span of about 0 to 25 Hz. In the experiment of FIG. 7, in the compression band 12 wound around a cylindrical artificial arm, for example, 100 mHg of pressurized air was supplied to the upstream expansion bag 22, the downstream expansion bag 26, and the detection expansion bag 24, respectively. In this state, when a pulse input having a constant volume of about 6 cc and a width of about 2 seconds is performed on a water bag disposed directly inside the detection expansion bag 24, the upstream expansion bag 22 and the downstream side are responded to the pulse input. The frequency spectrum of the pressure change which generate | occur | produces in the expansion bag 26 is shown. Further, in the experiment of FIG. 8, in the compression band 12 wound around the similar cylindrical artificial arm, the upstream inflation bag 22 and the downstream inflation bag 26 and the detection inflation bag 24 are pressurized air of, for example, 100 mHg. When a pulse input with a constant volume of about 6 cc and a width of about 2 seconds is performed on a water bag disposed directly under the upstream side expansion bag 22 in a state where each is supplied, a detection expansion bag is responded to it. 24 shows the frequency spectrum of the pressure change generated in the 24 and the downstream expansion bag 26. As is not clear from FIG. 7, the vibration transmission rate from the detection inflatable bag 24 to the upstream inflatable bag 22 and the downstream inflatable bag 26 is about −30 dB or less. Since the vibration transmission rate from the detection bag 22 to the detection expansion bag 24 and the downstream expansion bag 26 is also less than or equal to −30 dB, the interruption between them is preferably established.

  Returning to FIG. 1, in the circulatory information measuring device 14, the air pump 50, the quick exhaust valve 52, and the exhaust control valve 54 corresponding to the pressure control means are connected via a main pipe 56. From the main pipe 56, a first branch pipe 58 provided in series with a first on-off valve E1 for directly opening and closing between the air pump 50 and the upstream expansion bag 22 and connected to the upstream expansion bag 22, A volume pulse generator (EPG: volume pulse wave generator) 60 is provided in series to directly open and close the second branch pipe 62 connected to the detection expansion bag 24, and between the air pump 50 and the downstream expansion bag 26. For this purpose, a third branch pipe 64 provided in series with a third on-off valve E3 connected to the downstream expansion bag 26 is branched. Connected between the first branch pipe 58 and the second branch pipe 62 is a second on-off valve E2 for directly opening and closing the air pump 50 and the detection expansion bag 24. A main pressure sensor T0 for detecting the pressure in the main pipe 56 or an expansion bag connected thereto is connected to the main pipe 56, and a first pressure sensor T1 for detecting the pressure of the upstream side expansion bag 22 is provided. A second pressure sensor T2 connected to the upstream expansion bag 22 for detecting the pressure of the detection expansion bag 24 is connected to the detection expansion bag 24 and a third pressure sensor for detecting the pressure of the downstream expansion bag 26. A pressure sensor T3 is connected to the downstream expansion bag 26.

  Output signals of the main pressure sensor T0, the first pressure sensor T1, the second pressure sensor T2, and the third pressure sensor T3 are supplied to the electronic control unit 70. The electronic control unit 70 is a so-called microcomputer including a CPU 72, a RAM 74, a ROM 76, an I / O port (not shown), etc., and the CPU 72 uses the storage function of the RAM 74 to input signals according to a program stored in the ROM 76 in advance. By controlling the electric air pump 50, the quick exhaust valve 52, the exhaust control valve 54, the first on-off valve E1, the second on-off valve E2, the third on-off valve E3, and the volume pulse generator 60. The measurement data generated from the living artery 16 is collected, and the blood pressure value BP, the arterial flexibility (arterial compliance) K, and the pulse wave velocity PWV of the living body are calculated based on the measurement data. The measurement value that is the calculation result is displayed.

  FIGS. 9 and 10 are a flowchart and a time chart for explaining a main part of the control operation of the electronic control unit 70. FIG. When a power switch (not shown) is turned on, the initial state is shown at t0 in FIG. In this state, patient data input by the operator, such as sex, age, surname, patient ID, and the like are stored, and the first on-off valve E1, the second on-off valve E2, the third on-off valve E3, and the quick exhaust valve 52 are stored. Is a normally open valve, so that it is in a non-operating state, that is, an open state, and the exhaust control valve 54 is a normally closed valve, so that it is in a non-operating state, that is, a closed state. It is in an operating state. Next, when a startup operation device (not shown) is operated and the measurement operation of the circulatory information measuring device 14 is started, first, step S1 in FIG. 9 shown at times t1 to t3 in FIG. 10 (hereinafter, steps are omitted). The first blood pressure measurement routine is executed. This S1 corresponds to the oscillometric blood pressure measuring means, that is, the first blood pressure measuring means or the first blood pressure measuring step.

That is, first, at time t1 in FIG. 10, the air pump 50 is activated, and the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 communicated with the compressed air pumped from the air pump 50. Both of the pressures of the upper arm 10 are rapidly increased and compression of the upper arm 10 by the entire compression band 12 is started. When the pressure detected by the main pressure sensor T0, that is, the compression pressure Pe by the compression band 12, reaches a pressure increase target pressure Pmax set in advance to a value sufficiently higher than the maximum blood pressure value of the living body, the operation of the air pump 50 is stopped. In response to this, the exhaust control valve 54 is operated so that the compression pressure by the compression band 12 decreases at a constant speed, and the slow exhaust is started. Time t2 in FIG. 10 shows this state. In this slow exhaust process, the cuff pressure signal indicating the compression pressure (static pressure) by the compression band 12 is discriminated from the pressure signal output from the second pressure sensor T2 by performing low-pass filter processing. A pulse wave signal is discriminated by performing a band pass filter process for discriminating a signal in a wavelength band of Hz to several tens of Hz. Next, in accordance with an oscillometric blood pressure value determination algorithm executed every time the pulse wave signal is generated, the maximum blood pressure value BP _SYS (mmHg) and the average blood pressure value BP _MEAN based on the amplitude of the pulse wave signal generated sequentially or the change thereof. And the minimum blood pressure value BP _DIA (mmHg) is determined. At the same time as the minimum blood pressure value BP _DIA is determined, the quick exhaust valve 52 is opened, and in response, the exhaust control valve 54 is opened until it reaches its maximum opening. Thus, the first blood pressure measurement routine of S1 in FIG. 9 is terminated. Time t3 in FIG. 10 shows this state.

For example, the oscillometric blood pressure value determination algorithm uses the pressure indicated by the pressure signal corresponding to the maximum peak point of the differential waveform of the envelope when the envelope connecting the amplitude values of the pulse wave signal (envelope) rises rapidly. The value BP _SYS value (mmHg) is determined, the pressure indicated by the pressure signal corresponding to the maximum value of the envelope (envelope) connecting the amplitude values of the pulse wave signal is determined as the average blood pressure value BP _MEAN , and the pulse wave signal The pressure indicated by the pressure signal corresponding to the minimum peak point of the differential waveform of the envelope is determined as the diastolic blood pressure value BP _DIA . 11, FIG. 12 and FIG. 13 are discriminated by performing a band-pass filter on the pressure signal output from the first pressure sensor T1 when the compression pressure by the compression band 12 is 115 mmHg, 102 mmHg, and 60 mmHg. A pulse wave signal (broken line), a pulse wave signal (one-dot chain line) discriminated by the band-pass filter processing of the pressure signal output from the second pressure sensor T2, and a pressure signal output from the third pressure sensor T3 The pulse wave signal (two-dot chain line) discriminated by the band-pass filter processing and the pulse wave signal (solid line) discriminated by the band-pass filter processing of the pressure signal output from the main pressure sensor T0 FIG. 4 is a diagram showing normalization in the same phase for comparison. There is a difference in amplitude between these four types of pulse wave signals, and it is considered that the pulse wave signal obtained from the detection inflation bag 24 most accurately reflects the pulsation of the artery 16.

FIG. 14 is a diagram showing the envelopes formed by the amplitude values for each pressure value of the above four types of pulse wave signals, with the amplitudes normalized so that the relative value is “1” at 65 mmHg, so that they can be compared. According to each envelope, there is not much variation in the systolic blood pressure value BP _SYS , but extremely large variation occurs in the diastolic blood pressure value BP _DIA .

Next, the pulse wave velocity measurement routine of S2 in FIG. 9 is executed in the section shown at time t4 to t6 in FIG. This S2 corresponds to the pulse wave velocity measuring means or the pulse wave velocity measuring step. First, the quick exhaust valve 52 and the exhaust control valve 54 are closed and the air pump 50 is activated. Next, when the pressures of the upstream inflation bag 22, the detection inflation bag 24, and the downstream inflation bag 26 reach a pulse wave detection pressure Ppwv that is set to a value lower than the minimum blood pressure value BP _{DIA in} advance, for example, 60 mmHg, the first The on-off valve E1, the second on-off valve E2, and the third on-off valve E3 are closed, and the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 are maintained at the pulse wave detection pressure independently of each other. . This state is shown at time t5 in FIG. In this state, the pressure signals output from the first pressure sensor T1 and the third pressure sensor T3 are subjected to bandpass filter processing, thereby indicating pulse waves detected by the upstream expansion bag 22 and the downstream expansion bag 26. The pulse wave signals are discriminated, and the phase difference (pulse wave propagation time) Δt (sec) between these pulse wave signals and the center-to-center distance L (m) between the upstream expansion bag 22 and the downstream expansion bag 26 of about 90 mm, for example. Based on the above, the pulse wave velocity bbPWV (m / sec) is calculated from the equation (1). Such calculation of the pulse wave propagation velocity bbPWV is repeatedly executed every time a pulse wave is generated until time t6 is reached, and when it reaches, the average value of the pulse wave propagation velocity bbPWV obtained so far is calculated.

  bbPWV = L / Δt (1)

FIG. 15 shows the pulse wave propagation velocity bbPWV with respect to the trans- mural pressure TP (mmHg) which is the pressure difference of the artery wall of the artery 16 (= intra-arterial pressure or average blood pressure value BP _MEAN -external artery pressure or compression pressure Pe due to the compression band). The change is shown in comparison with the pulse wave velocity hbPWV from the conventional ECG R wave to the upstream inflation bag 22 measured from the same living body at the same time. As is clear from FIG. 15, the pulse wave propagation velocity hbPWV shows a substantially constant value regardless of the trans- mural pressure TP. On the other hand, the pulse wave velocity bbPWV shows a substantially constant value until the pressure of the transmural pressure TP reaches a negative value of 10 to 20 mmHg, that is, until the compression pressure by the compression band 12 reaches the minimum blood pressure value BP _DIA. There is a characteristic that it increases proportionally as it increases further. The pulse wave velocity bbPWV is obtained as a circulatory parameter for evaluating the hardening state of the artery 16 that can be compared for each individual by measuring a predetermined pressure value, for example, TP = 50 mmHg or a value near or at an increase rate. It is done.

Next, the second blood pressure measurement / arterial compliance data detection routine of S3 in FIG. 9 is executed in the section shown at time t7 to t9 in FIG. This S3 corresponds to the second blood pressure calculating means and the arterial compliance calculating means, or the second blood pressure calculating step and the arterial compliance data detecting step. In S3, as in the first blood pressure measurement routine, first, the air pump 50 is started at time t7, and the upstream expansion bag 22 and the detection expansion bag 24 that are in communication with the compressed air pumped from the air pump 50 are detected. , And the pressure of the downstream expansion bag 26 is rapidly increased, and the compression of the upper arm 10 by the entire compression band 12 is started. The pressure increase target preset by the pressure detected by the main pressure sensor P0, that is, the compression pressure Pe by the compression band 12, higher than the maximum blood pressure value BP _SYS of the living body, which is the previous measurement value by the first blood pressure measurement routine. When the pressure Pmax is reached, the operation of the air pump 50 is stopped, and in response to this, the exhaust control valve 54 is operated so that the compression pressure Pe by the compression band 12 is lowered at a constant speed, and per unit time or Slow exhaust at a constant speed per unit pulse wave is started. Time t8 in FIG. 10 shows this state. In this slow exhaust process, the pressure signal output from the second pressure sensor T2 is subjected to bandpass filter processing, so that the pulse wave signal indicating the pulse wave detected by the detection expansion bag 24 is repeatedly discriminated. . Next, in the same manner as in the first blood pressure measurement routine, the maximum blood pressure value BP is determined based on the amplitude of the pulse wave signal generated sequentially or the change thereof according to the oscillometric blood pressure value determination algorithm executed every time the pulse wave signal is generated. _SYS (mmHg), mean blood pressure value BP _SYS and diastolic blood pressure value BP _DIA (mmHg) are determined, and at the same time as the diastolic blood pressure value BP _DIA is determined, the quick exhaust valve 52 is opened, and in response thereto, the exhaust control valve 54 is opened until the maximum opening is reached, and the second blood pressure measurement routine of S3 in FIG. 9 is terminated. Time t9 in FIG. 10 shows this state. The pulse pressure is a pressure difference between systolic blood pressure values BP _SYS and diastolic blood pressure BP _DIA PP (= systolic blood pressure BP _SYS - diastolic blood pressure BP _DIA) is computed. For the calculation of the blood vessel compliance K described later, the pulse pressure PP (mmHg) based on the maximum blood pressure value BP _SYS and the minimum blood pressure value BP _DIA obtained from the second blood pressure measurement routine is used.

  Next, the cuff compliance calculation routine of S4 in FIG. 9 is executed from time t10 to t18 in FIG. This S4 corresponds to the cuff compliance calculating means or the cuff compliance calculating step. In S4, first, the air pump 50 is activated at time t10, and the pressures of the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 that are in communication with the compressed air pumped from the air pump 50 are detected. Both are rapidly raised and the compression of the upper arm 10 by the entire compression belt 12 is started. When the pressure detected by the main pressure sensor P0, that is, the compression pressure Pe by the compression band 12 reaches the first pressure P1 set in advance (time t11), the operation of the air pump 50 is stopped, and in response to this, The first on-off valve E1, the second on-off valve E2, and the third on-off valve E3 are closed, and the pressures of the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 remain at the first pressure P1 until time t12. Maintained. In the first pressure maintaining section between times t11 and t12, air having a constant volume C of, for example, about 0.2 cc is delivered from the volume pulse generator 60 at a timing corresponding to the bottom of the pulse wave in synchronization with the generation of the pulse wave. Is pulsed into the detection inflatable bag 24 in a width of 50 ms to 100 ms, and the signal output from the second pressure sensor T2 is subjected to band-pass filter processing, for example, the volume as shown in FIG. A pulse wave signal in which the pressure pulse Pp corresponding to the volume pulse applied from the pulse generator 60 is superimposed is obtained and stored. In this case, a plurality of about 10 pulse wave signals shown in FIG. 16 may be collected and stored in the pressure maintaining section, and those pulse wave signals may be stored, or the average value of the pulse wave signals may be stored. May be. Then, the time t12 is reached and the first pressure maintaining section ends.

The volume pulse injected from the volume pulse generator 60 into the detection inflation bag 24 is air of a constant volume C set in advance regardless of the pressure change of the detection inflation bag 24 at that time. Is set in advance to a value corresponding to the volume increase that is inflated in synchronization with the heartbeat and repeatedly applied to the detection inflatable bag 24. Further, the pulse wave signal shown in FIG. 16 is a pressure value, the systolic blood pressure value BP _SYS (mmHg) obtained in S1 is made to correspond to the upper peak value of the pulse wave signal, and the diastolic blood pressure value BP _DIA (mmHg) is changed to the pulse value. By making it correspond to the lower peak value of the wave signal, the vertical axis in FIG. 16 is converted into the maximum blood pressure value of the living body.

  At the time t12 when the first pressure maintaining section ends, the first on-off valve E1, the second on-off valve E2, and the third on-off valve E3 are opened again, and at the same time, the air pump 50 is started again. The pressures of the upstream inflation bag 22, the detection inflation bag 24, and the downstream inflation bag 26 in communication with each other are rapidly increased by the compressed air being compressed, and the compression of the upper arm 10 by the entire compression belt 12 is started. When the pressure detected by the main pressure sensor P0, that is, the compression pressure Pe by the compression band 12 reaches the second pressure P2 set in advance (time t13), the operation of the air pump 50 is stopped, and in response to this, The first on-off valve E1, the second on-off valve E2, and the third on-off valve E3 are closed, and the pressure in the upstream inflating bag 22, the detecting inflating bag 24, and the downstream inflating bag 26 reaches the second pressure P2 until time t14. Maintained. In the second pressure maintaining section, similarly to the first maintaining section, the constant volume C air from the volume pulse generator 60 is expanded in a pulsed manner with a width of 50 ms to 100 ms in synchronization with the generation of the pulse wave. The signal injected into the bag 24 and subjected to the band-pass filter process on the signal output from the second pressure sensor T2 corresponds to the volume pulse applied from the volume pulse generator 60 as shown in FIG. A pulse wave signal on which the pressure pulse Pp is superimposed is obtained and stored.

  Next, similarly, the pressures of the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 are increased to the preset third pressure P3 by the pressure detected by the main pressure sensor T0. At the same time, the third pressure P3 is maintained in the third pressure maintaining section t15 to t16, and in the third pressure maintaining section t15 to t16, air of a constant volume C from the volume pulse generator 60 is synchronized with the generation of the pulse wave. As shown in FIG. 16, which is obtained by injecting into the detection inflatable bag 24 in a pulse manner with a width of 50 ms to 100 ms, and subjecting the signal output from the second pressure sensor T2 to band-pass filtering. A pulse wave signal in which a pressure pulse Pp corresponding to the volume pulse applied from the volume pulse generator 60 is superimposed is obtained and stored. Similarly, the pressures of the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26 are increased to the preset fourth pressure P4 by the pressure detected by the main pressure sensor P0. At the same time, the fourth pressure P4 is maintained in the fourth pressure maintaining section t17 to t18. In the fourth pressure maintaining section t17 to t18, air of a constant volume C from the volume pulse generator 60 is synchronized with the generation of the pulse wave. As shown in FIG. 16, which is obtained by injecting into the detection inflatable bag 24 in a pulse manner with a width of 50 ms to 100 ms, and subjecting the signal output from the second pressure sensor T2 to band-pass filtering. A pulse wave signal in which a pressure pulse Pp corresponding to the volume pulse applied from the volume pulse generator 60 is superimposed is obtained and stored.

  The pulse wave signals detected and stored by the second pressure sensor T2 for each of the first pressure P1, the second pressure P2, the third pressure P3, and the fourth pressure P4 are derived from the pulsation of the artery 16. The generated pressure change width in the detection inflation bag 24, that is, the amplitude value ΔP (mmHg) of the pulse wave, that is, ΔP1, ΔP2, ΔP3, ΔP4 is calculated and stored. In addition, pressure pulses Pp corresponding to the volume pulses applied from the volume pulse generator 60 in each pulse wave signal, that is, Pp1, Pp2, Pp3, and Pp4, are calculated, respectively, and the cuff compliance Se (mmHg) of the detection expansion bag 24 is calculated. / Cc), that is, Se1, Se2, Se3, Se4 are calculated from the following equation (2) and stored. In the following equation (2), ΔPc is a volume pulse as shown in FIG. 16 under the compression pressure by the detection expansion bag 24, that is, under the first pressure P1, the second pressure P2, the third pressure P3, and the fourth pressure P4. In the pulse wave signal on which the pressure pulse Pp generated in response to the volume pulse applied from the generator 60 is superimposed, the pressure rise value (mmHg) of the pressure pulse Pp. C is a volume value (cc) of a pulse having a constant volume applied from the volume pulse generator 60. Therefore, the cuff compliance Se represents the sensitivity indicating the ratio of the pressure change to the volume change of the detection expansion bag 24. When the cuff compliance Se is obtained in this manner, the vertical axis, that is, the amplitude of the pulse wave detected by the second pressure sensor T2 from the detection expansion bag 24 can be converted into a volume. That is, the vertical axis in FIG. 11 can be converted into a volume axis.

  Se = ΔPc / C (2)

The preset first pressure P1 is a pressure lower than the minimum blood pressure value BP _DIA , for example, 50 mmHg, the second pressure P2 is a pressure higher than the first pressure P1, for example, the minimum blood pressure value BP _DIA , and the third pressure P3 is the second pressure. The pressure higher than P2, for example, the average blood pressure value BP _MEAN , and the fourth pressure P4 are set to a pressure higher than the third pressure P3, for example, a pressure 15 mmHg higher than the average blood pressure value BP _MEAN , respectively. Cuff compliance Se1, Se2, Se3, Se4 is required. These set pressures are values arbitrarily set in order to obtain the cuff compliance Se of the detection inflatable bag 24 that is different for each compression pressure Pe by the compression band 12.

Next, in S5 of FIG. 9, an arterial compliance calculation routine is executed. This S5, together with S3 and S4, constitutes an arterial compliance calculating means or an arterial compliance measuring step. In S5 of FIG. 9, first, based on the maximum blood pressure value BP _SYS and the minimum blood pressure value BP _DIA stored in S3, the pulse pressure PP (mmHg) of the living body is calculated from the following equation (3). Next, based on the pressure change width in the inflatable bag 24 for detection generated due to the pulsation of the artery 16, that is, the amplitude ΔP of the pulse wave and the cuff compliance Se, the following equation (4) Vessel volume change (amplitude value converted into volume unit) ΔV (cc or cm ³ ) is calculated, and vessel compliance K is detected from equation (5) based on the pulse pressure PP and vessel volume change ΔV. Each is calculated according to the compression pressure in the expansion bag 24. For example, the vascular compliance K1 at the first pressure P1 is calculated from the following equation (4) based on the amplitude ΔP1 of the pulse wave detected from the detection inflation bag 24 and the cuff compliance Se under the first pressure P1. 16 is obtained from the equation (5) based on the change in blood vessel volume ΔV1 per beat and the pulse pressure PP. Similarly, the blood vessel compliance K2 corresponding to the second pressure P2 is calculated, the blood vessel compliance K3 corresponding to the third pressure P3 is calculated, and the blood vessel compliance K4 corresponding to the fourth pressure P4 and the fourth pressure is calculated.

PP = BP _SYS −BP _DIA (3)
ΔV = ΔP / Se (4)
K = ΔV / PP (5)

Next, in S6 of FIG. 9, a display control routine is executed. This S6 is the pulse wave propagation velocity bbPWV in the brachial artery 16 measured in S2 or the rate of change thereof, the maximum blood pressure value BP _SYS and the minimum blood pressure value BP _{DIA of} the living body measured in S3, and the cuff measured in S4. The arterial compliances K1, K2, K3, K4 calculated in the compliances Se1, Se2, Se3, Se4, S5 are displayed on the display device 72 together with patient data such as the patient's sex, age, first name, and patient ID. Accordingly, the health status of the patient's circulatory system is objectively determined based on the pulse wave velocity bbPWV, the systolic blood pressure value BP _SYS, and the systolic blood pressure value BP _DIA , arterial compliances K1, K2, K3, and K4 displayed on the display device 72. Indicated.

  As described above, according to the present embodiment, the compression band 12 includes the pair of upstream inflatable bags 22 made of a flexible sheet that is positioned at a predetermined interval in the longitudinal direction of the upper arm 10 that is the compressed portion. The downstream inflatable bag 26 is disposed between the pair of upstream inflatable bags 22 and the downstream inflatable bag 26 so as to be continuous in the longitudinal direction of the upper arm 10 that is the pressed portion, and the pair of upstream inflatable bags 22 and And a detection expansion bag 24 having an air chamber independent of the downstream expansion bag 26, and the upper arm 10 of the living body is maintained at the same pressure by the upstream expansion bag 22, the detection expansion bag 24, and the downstream expansion bag 26. Since the pressure fluctuation in the detection inflation bag 24 is detected as the pulse wave in the compressed state, the upstream inflation bag 22, the detection inflation bag 24, which is continuous in the longitudinal direction of the upper arm 10, and the downstream Side expansion bag 26 While applying compressive pressure at a uniform pressure distribution with respect to the artery 16 in the upper arm 10 which is an object to be compression sites of Luo biological, accurate pulse wave is obtained.

  Further, according to the compression band 12 of the present embodiment, the flexible sheet is folded in the direction approaching each other at both end portions 24a and 24b of the detection inflatable bag 24 in the longitudinal direction of the upper arm 10 which is a pressed portion. A pair of folding grooves 24f and 24f are formed, and adjacent end portions 22a and 26a on the side adjacent to the detection inflation bag 24 of the upstream inflation bag 22 and the downstream inflation bag 26 are formed in the pair of folding grooves 24f. 24f, both end portions 24a, 24b of the detection inflatable bag 24 and the adjacent end portions 22a and 26a of the upstream inflatable bag 22 and the downstream inflatable bag 26 are the upper arms that are compressed parts. 10 are overlapped in the radial direction, so that even in the vicinity of the boundary between the detection inflating bag 24 and the upstream inflating bag 22 and the downstream inflating bag 26, a uniform compression pressure is applied to the upper arm 10. Cloth can be obtained.

  Further, according to the compression band 12 of the present embodiment, at least one of the opposed groove side surfaces of the pair of folding grooves 24f, 24f of the detection expansion bag 24 and the upstream side inserted into the folding grooves 24f, 24f. Rigid anisotropy between the expansion bag 22 and the adjacent side end portions 22a and 26a of the downstream expansion bag 26 having higher bending rigidity in the width direction of the compression band 12 than in the longitudinal direction of the compression band 12 In particular, a low frequency pressure vibration noise shielding action from the upstream inflatable bag 22 and the downstream inflatable bag 26 to the detection inflatable bag 24 is suitably obtained. Therefore, it is possible to obtain an accurate pulse wave that is hardly affected by pressure vibration noise of a relatively low frequency.

  Further, according to the compression band 12 of the present embodiment, the longitudinal shielding member 42 is arranged in the circumferential direction of the upper arm 10 in a state where a plurality of flexible hollow tubes 44 parallel to the longitudinal direction of the upper arm 10 are parallel to each other. Since they are configured by being arranged in series, a low frequency pressure vibration noise shielding action from the upstream expansion bag 22 and the downstream expansion bag 26 to the detection expansion bag 24 can be more suitably obtained. Thus, a more accurate pulse wave that is not easily affected by pressure vibration noise of a relatively low frequency can be obtained.

  Further, according to the circulatory organ information measuring device 14 provided with the compression band 12 of this embodiment, that is, the blood pressure measuring device, the detection inflating bag 24 and the second pressure sensor T2 for detecting the pressure in the detecting inflating bag 24. And pressurizing the artery 16 in the upper arm 10 which is a compressed part by pressurizing the pair of upstream inflatable bag 22 and downstream inflatable bag 26 and the detecting inflatable bag 24 in communication with each other, Exhaust control valve (pressure control means) 54 for continuously changing the compression pressure Pe, and pressure oscillation of the compression pressure Pe detected by the second pressure sensor T2 in the process in which the compression pressure Pe is changed by the exhaust control valve 54 Since the pulse wave which is a component is extracted by the band pass filter process, and an oscillometric blood pressure measuring means for determining the blood pressure value of the living body based on the change of the pulse wave, the pulse wave is obtained from the detection expansion bag 24. A highly accurate blood pressure value is obtained based on the accurate pulse wave.

Further, according to the circulatory organ information measuring device 14 provided with the compression band 12 of this embodiment, that is, the blood vessel flexibility measuring device, the pulse wave amplitude value ΔP detected by the pulse wave detecting means and the automatic blood pressure measuring device Since it includes arterial compliance calculating means S3 to S5 for calculating arterial compliance K indicating the flexibility of the artery 16 based on the measured maximum blood pressure value BP _SYS and minimum blood pressure value BP _DIA, it is obtained from the detection inflation bag 24. Based on the accurate high blood pressure value BP _SYS and minimum blood pressure value BP _DIA calculated from the accurate pulse wave and the change of the pulse wave, a high-precision arterial compliance K indicating the flexibility of the artery 16 is obtained. It is done.

Further, according to the circulatory organ information measuring device 14 provided with the compression band 12 of the present embodiment, that is, the vascular flexibility measuring device, the arterial compliance calculating means is based on the relationship between the pressure change and the volume change of the detection inflation bag 24. A cuff compliance calculating means S4 for calculating a cuff compliance Se for converting the pulse wave amplitude value ΔP from a pressure unit to a volume unit, and a blood vessel volume change ΔV which is an amplitude value of the pulse wave converted to the volume unit; Since the arterial compliance K indicating the flexibility of the artery is calculated based on the pressure difference between the systolic blood pressure value BP _SYS and the systolic blood pressure value BP _DIA detected by the automatic blood pressure measuring device, that is, the pulse pressure PP, More accurate arterial flexibility is obtained.

  Further, according to the circulatory organ information measuring device 14 provided with the compression band 12 of this embodiment, that is, the vascular flexibility measuring device, a predetermined volume of gas having a predetermined size corresponding to the pulsation of the artery 16 is used for the detection. A volume pulse generator (constant volume pulse wave generator) 60 to be added into the expansion bag is provided, and the cuff compliance calculation means S4 has a volume of a certain volume of gas added to the detection expansion bag 24 by the volume pulse generator 60. The relationship between the value C and the pressure increase value ΔPc in the detection expansion bag 24 detected by the second pressure sensor T2 when the gas of the fixed volume C is added into the detection expansion bag 24 is obtained in advance. Therefore, the cuff compliance Se of the inflatable bag 24 for detection is, for example, in response to a preset constant cycle, pulse, or pressure change value, for example. Each time a constant volume of gas is added from 0 to the inflatable bag 24 for detection, the average value is obtained when a plurality of gases are obtained.

Further, according to the circulatory organ information measuring device 14 provided with the compression band 12 of this embodiment, that is, the pulse wave velocity measuring device, the pressure in the compression band 12 for detecting the pulse wave and the pressure in the upstream expansion bag 22 are detected. The first pressure sensor T1, the third pressure sensor T3 for detecting the pressure in the downstream expansion bag 26, and the gas in the upstream expansion bag 22 and the downstream expansion bag 26 at a pressure lower than the minimum blood pressure value BPDIA of the living body. , The pulse wave propagation time Δt from the pulse wave detected by the first pressure sensor T1 to the pulse wave detected by the third pressure sensor T3 in the state of being filled with the upstream expansion bag 22 and the downstream expansion bag 26 And a pulse wave velocity measuring means S2 for calculating the pulse wave velocity bbPWV in the artery 16 based on the center-to-center distance L between the two, so that the local pulse of the artery 16 in the upper arm 10 of the living body is included. Wave propagation velocity value bbPWV is easily obtained It is. Preferably, the pulse wave propagation time Δt from the pulse wave detected by the first pressure sensor T1 to the pulse wave detected by the third pressure sensor T3 in a state where the inside of the detection expansion bag 24 is exhausted is calculated. . In this way, the space between the upstream expansion bag 22 and the downstream expansion bag 26 is sufficiently shielded, so that the detected pulse wave is accurate, and the pulse wave propagation velocity bbPWV with higher accuracy is obtained.

In general, there is a phenomenon in which the second blood pressure measurement value decreases and then stabilizes when blood pressure measurement is repeated, which is considered to be caused by the aging of the vascular system of the living body or the familiarity of the compression band 12. According to the present embodiment, the maximum blood pressure value BP _SYS (mmHg), the average blood pressure value BP _SYS, and the minimum blood pressure obtained by the second blood pressure measurement routine executed in S3 after the first blood pressure measurement routine in S1 is executed. Since the value BP _DIA (mmHg) is used for the calculation of the blood vessel compliance K, a comparatively constant height that avoids a decrease in the accuracy of the blood pressure measurement value due to the above phenomenon by temporarily pressing the pressure band 12 above the maximum blood pressure value. The maximum blood pressure value BP _SYS (mmHg), the average blood pressure value BP _MEAN, and the minimum blood pressure value BP _DIA (mmHg) can be obtained and used for the calculation of the blood vessel compliance K. Can be increased.

  Further, in the present embodiment, as shown in FIG. 10, as the last step in the step of compressing the upper arm 10, the first pressure P1, the second pressure P2, the third pressure P3, and the fourth pressure P4 are stepped. Since the cuff compliance measurement of S4 to be maintained is executed, the pulse wave is generated in a state where the physiological fluctuation of the living body does not occur by executing the process with the greatest burden on the living body last. There is an advantage that can be collected.

  In addition, according to the circulatory organ information measuring device 14 provided with the compression band 12 of this embodiment, that is, the vascular flexibility measuring device, the cuff compliance calculating means corresponding to S4 has the first pressure P1, the second pressure P2, the first Since a pulse wave is collected from the detection expansion bag 24 within a period in which the pressures P3 and P4 are maintained constant, a pulse wave without distortion can be obtained, so that a more accurate blood vessel compliance K can be obtained. There is an advantage that can be obtained.

  As mentioned above, although one Example of this invention was described based on drawing, this invention can be implemented also in another aspect.

  For example, the compression band 12 of the above-described embodiment is for the upper arm, but may be a compression band for the forearm or the lower limb.

  2 to 6 described above, the longitudinal shielding member 42 interposed between the upstream inflating bag 22 and the downstream shielding bag 26 and the detection shielding bag 24 is provided on the upper arm 10. You may be comprised from the comparatively hard longitudinal-shaped resin sheet which is arrange | positioned in the circumferential direction and in which the many groove | channels were formed in the longitudinal direction, ie, the width direction, at fixed intervals. In short, what is necessary is just to have anisotropy of rigidity in which the bending rigidity in the width direction of the compression band 12 is higher than the bending rigidity in the longitudinal direction of the compression band 12. The longitudinal shielding member 42 may have a length similar to that of the upstream inflating bag 22 and the downstream shielding bag 26 or the detection shielding bag 24, but may be shorter than that. The effect is obtained. For example, a plurality of, for example, two or three may be arranged at regular intervals in the circumferential direction of the upper arm 10.

In the above-described embodiment, the maximum blood pressure value BP _SYS (mmHg), the average blood pressure value BP _MEAN and the minimum blood pressure value BP _DIA (mmHg) determined by the second blood pressure measurement routine of S3 in FIG. The maximum blood pressure value BP _SYS (mmHg), the average blood pressure value BP _MEAN, and the minimum blood pressure value BP _DIA (mmHg) determined by the first blood pressure measurement routine of S1 in FIG. May be used. In this case, the second blood pressure measurement routine may not be provided.

  Further, in the above-described embodiment, since the pulse wave can be collected in the process in which the pressure in the detection inflating bag 24 gradually drops, the cuff compliance calculating means corresponding to S4 is the first corresponding to S3. It may be executed in the same section as the two blood pressure measurement means. Further, the cuff compliance calculating unit corresponding to S4 may be executed before the second blood pressure measuring unit corresponding to S3.

  In the above-described embodiment, four stages of the first pressure P1, the second pressure P2, the third pressure P3, and the fourth pressure P4 are used as pressures for obtaining the cuff compliance Se. Since it is a value for determining the cuff compliance Se of the detection inflatable bag 24 that is different for each compression pressure Pe by the compression band 12, it can be arbitrarily set to the compression pressure Pe of the compression band 12 on which the arterial compliance K is determined. For example, if the compression pressure of the compression band 12 on which the arterial compliance K is calculated is one stage of a predetermined pressure, the pressure in the pressure maintaining section for measuring the cuff compliance Se is one stage, and if the three stages are the above, The pressure in the pressure maintaining section for measuring the cuff compliance Se is three stages, and if it is five stages, the pressure in the pressure maintaining section for measuring the cuff compliance Se is five stages.

In the above-described embodiment, in the first blood pressure measurement routine of S1 and the second blood pressure measurement routine of S3 in FIG. 9, the maximal blood pressure value BP _SYS and the minimum blood pressure value are determined using the oscillometric method based on the change in the amplitude of the pulse wave. The BP _DIA has been determined. The oscillometric method is used to determine the minimum blood pressure value BP _DIA and the maximum blood pressure based on the change in the integrated value of the pulse wave, that is, the change in the area of the surface formed by the pulse wave graph on the time axis. The value BP _SYS may be determined, or the minimum blood pressure value BP _DIA and the maximum blood pressure value BP _SYS may be determined based on the occurrence and disappearance of Korotkoff sounds detected by a microphone.

  The above description is merely an example of the present invention, and various modifications can be made without departing from the spirit of the present invention.

It is a block diagram explaining the structure of the circulatory organ information measuring device provided with the compression band to which this invention was applied. It is a figure which cuts off the outer side of the compression belt with which the circulatory organ information measuring apparatus of FIG. It is a figure which shows the inner side of the compression band with which the circulatory organ information measuring apparatus of FIG. 1 was equipped. FIG. 3 is a diagram showing a part of an upstream inflatable bag, a detection inflatable bag, and a downstream inflatable bag accommodated in the compression band shown in FIGS. 1 and 2. FIG. 5 is a cross-sectional view illustrating the configuration of the upstream expansion bag, the detection expansion bag, and the downstream expansion bag in FIG. 4, and is a view taken along the line VV in FIG. 4. It is a perspective view which shows the upstream expansion bag, the detection expansion bag, and the downstream expansion bag which were accommodated in the compression belt | band | zone shown in FIG. 1 and FIG. 2, respectively. FIG. 3 is a diagram illustrating a transmission rate of noise from a detection expansion bag to an upstream expansion bag or a downstream expansion bag in the compression band illustrated in FIGS. 1 and 2. FIG. 3 is a diagram illustrating a transmission rate of noise from an upstream expansion bag to a detection expansion bag or a downstream expansion bag in the compression band illustrated in FIGS. 1 and 2. It is a flowchart explaining the principal part of the control action of the electronic controller of FIG. It is a time chart explaining the principal part of the control action of the electronic controller of FIG. In the circulatory organ information measurement apparatus of FIG. 1, when the pressure applied to the upper arm is 115 mmHg, pulse waves discriminated from the output signals of the main pressure sensor, the first pressure sensor, the second pressure sensor, and the third pressure sensor are detected. It is a figure shown on a common time-axis. In the circulatory information measuring apparatus of FIG. 1, when the pressure applied to the upper arm is 102 mmHg, pulse waves discriminated from the output signals of the main pressure sensor, the first pressure sensor, the second pressure sensor, and the third pressure sensor are detected. It is a figure shown on a common time-axis. In the circulatory organ information measuring apparatus of FIG. 1, when the pressure applied to the upper arm is 60 mmHg, the pulse wave discriminated from the output signals of the main pressure sensor, the first pressure sensor, the second pressure sensor, and the third pressure sensor is detected. It is a figure shown on a common time-axis. In the blood pressure measuring means corresponding to S1 and S3 in FIG. 9, the amplitude of the pulse wave discriminated from the output signals of the main pressure sensor, the first pressure sensor, the second pressure sensor, and the third pressure sensor in the slow-down pressure flow. It is a figure which shows an envelope on a common compression pressure axis. The relationship between the pulse wave velocity bbPWV obtained by the pulse wave velocity measuring means corresponding to S2 in FIG. 9 and the transmural pressure TP is compared with the pulse wave velocity hbPWV from the R wave of the ECG to the upstream inflation bag. FIG. It is a figure which illustrates the waveform of the pulse wave detected by the 2nd pressure sensor when the pulse of a fixed volume is inputted into the expansion bag for detection for cuff compliance measurement in S4 of FIG.

Explanation of symbols

10: Upper arm (stressed part of living body)
12: Compression band (Pulse wave detection compression band)
14: Cardiovascular information measuring device (automatic blood pressure measuring device, vascular flexibility measuring device, pulse wave velocity measuring device)
22: upstream side expansion bags 22a, 26a: adjacent side end 24: detection expansion bag 24a, 24: both ends 24f: folding groove 26: downstream side expansion bag 42: longitudinal shielding member 44: flexible hollow tube 54: Exhaust control valve (pressure control means)
60: Volume pulse generator (constant volume pulse wave generator)
82: Main expansion bag 84: Detection expansion bag T1: First pressure sensor T2: Second pressure sensor (pressure sensor)
T3: third pressure sensor S1, S3: oscillometric blood pressure measuring means S3, S4, S5: arterial compliance calculating means S4: cuff compliance calculating means S2: pulse wave velocity measuring means

Claims (8)

A pulse wave detection compression band wound around a compressed portion of the living body in order to detect a pulse wave generated from an artery of the living body,
A pair of upstream inflation bag and downstream inflation bag made of a flexible sheet positioned at a predetermined interval in the longitudinal direction of the pressed portion;
Detection that has an air chamber that is arranged between the pair of upstream inflation bags and the downstream inflation bag so as to be continuous in the longitudinal direction of the compressed portion, and is independent of the pair of upstream inflation bags and the downstream inflation bag. Including inflatable bags,
The pressure fluctuation in the detection expansion bag is detected as the pulse wave in a state where the compressed portion of the living body is compressed with the same pressure by the upstream expansion bag, the detection expansion bag, and the downstream expansion bag. ,
A pair of folding grooves formed of flexible sheets folded in directions approaching each other are formed at both ends of the detection inflation bag in the longitudinal direction of the pressed portion,
The pulse wave detection compression band , wherein adjacent end portions of the upstream expansion bag and the downstream expansion bag adjacent to the detection expansion bag are inserted into the pair of folding grooves . Between at least one of the opposing groove side surfaces of the pair of folding grooves of the detection expansion bag and the adjacent side ends of the upstream expansion bag and the downstream expansion bag inserted into the folding groove, to claim 1, elongated shielding member having a longitudinal bending stiffness is high stiffness anisotropy of the width of the cuff than the rigidity of the pulse wave detection cuff is characterized by being interposed The compression band for pulse wave detection as described. The longitudinal shielding member is configured by arranging a plurality of flexible hollow tubes parallel to the longitudinal direction of the compressed part and being arranged in a row in the circumferential direction of the compressed part in a state parallel to each other. The pulse wave detection compression band according to claim 2 , wherein the compression band is one. An automatic blood pressure measurement apparatus comprising the pulse wave detection compression band according to any one of claims 1 to 3 ,
A pressure sensor for detecting the pressure in the detection inflation bag;
The pressure in the compressed portion is compressed by increasing the pressure in a state where the pair of the upstream inflation bag and the downstream inflation bag are in communication with each other, and the compression pressure is continuously changed. Pressure control means;
A pulse wave that is a pressure oscillation component of the compression pressure detected by the pressure sensor in the process of changing the compression pressure by the pressure control means is extracted, and the blood pressure value of the living body is determined based on the change of the pulse wave. And an oscillometric blood pressure measuring means. A blood vessel flexibility measuring device comprising the automatic blood pressure measuring device according to claim 4 ,
Arterial compliance for calculating arterial compliance indicating flexibility of the artery based on an amplitude value of a pulse wave that is a pressure vibration component of compression pressure detected by the pressure sensor and a blood pressure value measured by the automatic blood pressure measurement device A blood vessel flexibility measuring device including a calculating means. The arterial compliance calculating means includes cuff compliance calculating means for calculating a cuff compliance for converting the amplitude value of the pulse wave from a pressure unit to a volume unit from the relationship of the pressure change with respect to the volume change of the detection inflation bag, Based on the amplitude value of the pulse wave converted into a unit and the pulse pressure that is the pressure difference between the maximum blood pressure value and the minimum blood pressure value detected by the automatic blood pressure measurement device, the arterial compliance indicating the flexibility of the artery is calculated. The vascular flexibility measuring device according to claim 5 , wherein A constant volume pulsation generator for adding a predetermined volume of gas of a size corresponding to the pulsation of the artery into the detection inflation bag;
The cuff compliance calculating means includes a volume value of a fixed volume of gas added to the detection inflatable bag by the constant volume pulse wave generator, and when the constant volume of gas is added to the inflatable bag for detection. The blood vessel flexibility measuring device according to claim 6 , wherein a relationship with a pressure increase value in the detection inflation bag detected by the pressure sensor is obtained in advance. A pulse wave velocity measuring device comprising the pulse wave detection compression band according to any one of claims 1 to 3 ,
A first pressure sensor for detecting a pressure in the upstream expansion bag;
A third pressure sensor for detecting the pressure in the downstream expansion bag;
Detected by the third pressure sensor from the pulse wave detected by the first pressure sensor in a state in which the upstream inflation bag and the downstream inflation bag are filled with gas at a pressure lower than the minimum blood pressure value of the living body. Pulse wave velocity measuring means for calculating the pulse wave velocity in the artery based on the pulse wave propagation time until the pulse wave and the center-to-center distance between the upstream inflation bag and the downstream inflation bag And a pulse wave velocity measuring device comprising:

Images