JP3219325B2 - Respiratory rate measuring device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an apparatus for easily measuring a respiratory rate of a living body from a circulatory organ of the living body.

[0002]

2. Description of the Related Art As an apparatus for measuring the respiratory rate of a living body,
A device that determines the respiratory rate based on the change cycle of the temperature of expiration and inspiration, a device that determines the respiratory rate based on the change cycle of the movement of the thorax detected by a rubber tube wound around the living chest, the impedance of the living chest An apparatus for determining a respiratory rate based on a change cycle of a circumstance has been proposed.

[0003]

However, the above-mentioned conventional respiratory rate measuring apparatus still has the following problems. That is, in a device that determines the temperature of exhalation and inhalation based on a change cycle of the temperature, the thermistor is attached to the nose by a clip in order to position a temperature sensor such as a thermistor for detecting the temperature of exhalation and inhalation in the nostril of the living body Therefore, there is a drawback that pain and discomfort are given to the living body. In addition, in a device that determines based on the change period of the movement of the rib cage detected by the rubber tube wound around the living rib cage, handling of the rubber tube is complicated, and it cannot be used for those having a disorder in the abdomen or chest. There was a disadvantage.
In addition, in the device that determines based on the change cycle of the impedance of the living chest, the respiratory variability impedance is detected by the electrode attached to the chest, so that only the discomfort caused by attaching the electrode to the chest is given to the living body. There is a drawback that it is inconvenient because the chest of the living body must be exposed without any problem.

The present invention has been made in view of the above circumstances, and has as its object to provide a breathing apparatus which is easy to handle, has no restriction on the use of the substance, and does not cause discomfort to the living body. A number measuring device is provided.

[0005]

A first object of the present invention to achieve the above object is to provide an apparatus for measuring a respiratory rate of a living body, wherein (1) a peripheral part of the living body. Pulse rate detecting means for sequentially calculating the pulse rate of the living body from the pulse wave continuously generated in synchronization with the heartbeat from (2) a pressure pulse continuously generated in synchronization with the heartbeat from the artery of the limb of the living body A systolic blood pressure value detecting means for sequentially obtaining a systolic blood pressure value of the living body from the wave size; (3) a multiplying value calculating means for calculating a multiplying value of the pulse rate and the systolic blood pressure value; and (4) a multiplied value thereof. Respiratory rate calculating means for calculating the respiratory rate of the living body according to the pulsation cycle of the multiplied value calculated by the calculating means.

[0006]

In this manner, the multiplication value calculating means calculates the multiplication value of the pulse rate sequentially obtained by the pulse rate detecting means and the systolic blood pressure value sequentially obtained by the systolic blood pressure detecting means, and calculates the respiratory rate. The calculating means calculates the respiratory rate of the living body according to the pulsation cycle of the multiplied value.

[0007]

The pulse rate detecting means is for sequentially obtaining a pulse rate from a pulse wave continuously generated in synchronization with a heartbeat from the peripheral part of the living body. since it is intended to determine the size or et systolic blood pressure pulse wave continuously generated in synchronism with heartbeat of the extremities of the artery sequentially for the measurement of respiratory rate, temperature sensor attached by clips to the nose of a living body There is no need to wrap the rubber tube around the chest or to expose the chest and attach electrodes to it, making it easier to handle, reducing the restrictions on the objects to be used, and causing discomfort to the living body. This is resolved.

Preferably, the multiplication value calculating means calculates the pulse rate as PR (t) and the systolic blood pressure value as SYS.
(t), the multiplied value N-PRP according to Equation 2
(t) is calculated.

[0009]

(Equation 2)

[0010]

Another object of the present invention to achieve the above object is to provide an apparatus for measuring a respiratory rate of a living body, which comprises: (2) a pulse wave detecting means for sequentially detecting a pulse wave continuously generated in synchronization with the heartbeat of the subject; and (2) a predetermined time elapse from the maximum peak position in the pulse wave detected by the pulse wave detecting means.
Determine the area of the interzone, pulse wave shape change detection means to detect the shape change of each pulse wave by the value of this area , (3) according to the pulse wave shape change cycle detected by the pulse wave shape change detection means Respiratory rate calculating means for calculating the respiratory rate of the living body.

[0011]

With this configuration, the pulse wave shape change detecting means detects a change in the shape of the pulse wave detected by the pulse wave detecting means, and the respiratory rate calculating means detects the change in the pulse wave shape by the pulse wave shape change detecting means. The respiratory rate of the living body is calculated according to the pulse wave shape change cycle.

[0012]

Since the pulse wave detecting means is for sequentially obtaining pulse waves which are attached to a living body and are continuously generated in synchronization with the heartbeat, the temperature sensor is used for measuring the respiratory rate. This eliminates the need to attach clips to the nose of a living body, wrap a rubber tube around the chest, or attach electrodes to the chest to expose it, making it easier to handle and reducing restrictions on the objects to be used. Moreover, the discomfort of the living body is eliminated.

Here, the pulse wave detecting means is preferably
Detects fingertip pulse wave, plethysmogram, photoelectric pulse wave of the toes of the living body, or is worn on the radial artery of the wrist of the living body or on the dorsal artery of the foot of the living body, and is generated from the artery. Detect pressure pulse wave.

Preferably, the pulse wave shape change detecting means obtains an area of a predetermined time zone which elapses from the maximum peak position of the pulse wave, and the shape value of each pulse wave is represented by the value of the area. Things.

[0015]

[0016]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the present invention will be described below in detail with reference to the drawings.

FIG. 2 is a block diagram illustrating the configuration of the respiratory rate measuring apparatus according to the present invention. In FIG. 2, a pulse wave sensor 10 is configured in the same manner as that described in, for example, Japanese Patent Application Laid-Open No. 4-67839, and has a pressing plane for detecting a pressure pulse wave generated from a radial artery. A pressure member having a plurality of pressure detecting elements arranged in a direction orthogonal to the radial artery, and a pressing device for pressing the pressing member onto the radial artery. The band 12 is attached to the wrist of the living body. The pulse wave sensor 10 is disclosed in, for example, Japanese Patent Application Laid-Open No. 1-1505 or Japanese Patent Application Laid-Open No. 2-109540.
As described in the publication, as a result of the pressing force of the pressing member being maintained at an optimum value so that a part of the radial artery becomes flat, the pressing force is detected by the pressure detecting element located immediately above the radial artery. The pressure value, that is, the value of the pressure pulse wave directly represents the blood pressure value in the radial artery. Therefore, the upper and lower peak values of the pressure pulse wave detected as described above indicate the systolic blood pressure value SYS and the diastolic blood pressure value DIA, respectively. FIG. 3 shows an example of the pressure pulse wave.

The pulse wave signal SM output from the pulse wave sensor 10 is supplied to a measuring circuit 14 for measuring a respiratory rate. The measurement circuit 14 includes an amplification circuit 16 that amplifies the input pulse wave signal SM, an A / D converter 18 that converts the amplified pulse wave signal SM into a digital signal, and a CPU 2.
0, a ROM 22, a RAM 24, and an output interface circuit 26. These CPU 20, ROM 22,
The RAM 24 and the output interface circuit 26 constitute a so-called microcomputer. The CPU 20 includes:
While using the RAM24 of temporary storage function in advance ROM22
The respiratory rate is calculated by processing the input signal in accordance with the program stored in the storage device, and the calculation result is output to the display 28, and simultaneously or as necessary to other devices.

FIG. 1 is a functional block diagram for explaining the function of the respiratory rate measuring apparatus according to the present embodiment. In the figure, the pulse rate detecting means 30, the time between upper peaks or the lower peaks of the pulse wave signal SM, i.e., obtains the wave period T _M, the wave cycle T pulse rate per minute from _M PR (= 60 / T
_R ) is calculated sequentially. The pulse rate thus determined continuously is represented as a function of time PR (t). The systolic blood pressure value detecting means 32 obtains the upper peak value of the pulse wave signal SM according to a well-known algorithm, and sequentially determines the systolic blood pressure value SYS which is the upper peak value. The continuously obtained systolic blood pressure value is also a function of time SYS.
(t). The N-PRP calculating means 34 calculates N-PRP (t) based on the pulse rate PR (t) and systolic blood pressure SYS (t) sequentially obtained from the following equation (1). Then, the respiration rate calculating means 36 calculates the N-PR
The period T _R (second) of the wave of P (t) is sequentially obtained, and
Respiratory rate R per minute for example on the basis of the period T _R
R (= 60 / T _R ) is continuously calculated. FIG. 4 shows the pulse rate PR (t), systolic blood pressure value SYS (t), N-PRP
It is a time chart which shows an example of (t). In the following equation (1), n is a number larger than 1 for reducing the weight of SYS (t), and for example, "2" is used. Also, i is the pulse rate PR (t) and systolic blood pressure value SYS.
This is a preset value corresponding to the phase difference with (t). The value i may be a preset constant value, or may be a value automatically obtained from the actual pulse rate PR (t) and systolic blood pressure value SYS (t) according to a program stored in advance.

[0020]

(Equation 3)

Next, the operation of the measuring circuit 14 will be described with reference to the flowchart of FIG. In the figure, step SS
At 1, it is determined whether or not the pulse wave signal SM has been input from the pulse wave sensor 10, in other words, whether or not the upper peak of the pulse wave signal SM has been detected. If the determination in step SS1 is negative, the process waits until pulse wave signal SM is input. However, if the determination in step SS1 is affirmed, in step SS2 corresponding to the pulse rate detecting means 30, the time between the upper peak or the lower peak of the pulse wave signal SM from the pulse wave sensor 10, A period T _M is obtained, and a pulse rate per minute PR (= 60 / T _R ) is sequentially calculated from the wave period T _M.
The pulse rate PR (t) shown in FIG. 4 shows the pulse rate thus obtained continuously as a function of time.

In step SS3 corresponding to the systolic blood pressure value detecting means 32, the upper peak value of the pulse wave signal SM is determined according to a well-known algorithm, and the upper peak value systolic blood pressure value SYS is sequentially determined. Is done. FIG.
The systolic blood pressure value SYS (t) indicates the systolic blood pressure value thus obtained continuously as a function of time.
Next, in step SS4 corresponding to the N-PRP calculating means 34 , N-PRP (N-PRP (T) is calculated based on the above-described pulse rate PR (t) and systolic blood pressure value SYS (t) sequentially obtained from the above equation (1). t) is calculated.

In the following step SS5, the pulse rate PR
(t) and at least one of systolic blood pressure values SYS (t), that is, whether or not the amplitude of the wave is smaller than a predetermined value. If the determination in step SS5 is negative, N-PR is determined in step SS6.
After the median filter processing for smoothing the waveform of P (t) is performed, the N-PR
The detection of the upper peak of the P (t) wave is performed. But,
If the determination in step SS5 is affirmative, step S S 7 remains median filter processing in step SS6 is not executed is executed. The median filter processing is to compare adjacent odd-numbered points among data points constituting N-PRP (t), and replace an intermediate value among the odd-numbered points as data of a center point of the odd-numbered points. Things.

[0024] If the determination in step SS7 is affirmative, at step SS8, N-PRP (t) a new period T _Rn determined based on the detection point P _U on the peak of
Is less than or equal to の of the shortest cycle of the pulse rate PR (t) and the blood pressure value SYS (t). This step SS8 is for removing abnormal upper peak judgment. If the determination in step SS8 is affirmative, steps SS1 and subsequent steps are executed again. However, if the determination in step SS8 is denied,
In step SS9, from the relationship shown in the following equation (2),
The above wave cycle of N-PRP (t), that is, respiratory cycle T
The respiration rate RR per minute is calculated based on _Rn, and the value of the respiration rate RR is displayed on the display 28.
Here, in the following equation (2), T _Rn-3 is the cycle obtained in the cycle three times before, T _Rn-2 is the cycle obtained in the cycle two times before, and T _Rn-1 is the cycle obtained one time before. Is the cycle determined in. In this flowchart, the above steps SS7, SS8, SS9 correspond to the respiratory rate calculating means 36.

[0025]

(Equation 4)

If the determination in step SS7 is negative, in step SS10 the elapsed time from the upper peak point of N-PRP (t) obtained in the previous cycle is determined by the period obtained in the previous cycle. T _Rn-1
Is determined, and whether the upper peaks of the pulse rate PR (t) and the blood pressure value SYS (t) are formed without abnormality. If the determination in step SS10 is denied,
Since it is a state in which it is estimated that there is no actual breathing, the above-mentioned steps SS1 and subsequent steps are repeatedly executed. However, if the determination in step SS10 is affirmative, NP
Since the upper peak point of RP (t) has not been clearly formed, it is assumed that the upper peak point of N-PRP (t) has been detected at the same cycle as that of the previous cycle.
Is executed.

By repeatedly executing the above steps, the pulse rate PR (t) and the systolic blood pressure value detecting means 3 sequentially obtained by the pulse rate detecting means 30 from the equation (1) are obtained.
N-PRP (t) is calculated on the basis of the systolic blood pressure value SYS (t) sequentially obtained in step 2, and the respiratory rate calculating means 36 calculates the respiratory rate RR of the living body in accordance with the pulsation cycle of the N-PRP (t). Is calculated. Here, in the respiratory rate measuring apparatus of the present embodiment, the pulse wave sensor 10 only needs to be attached to the wrist when measuring the respiratory rate, so that the temperature sensor is attached to the nose of the living body with a clip, or a rubber tube is attached to the chest. It is not necessary to wind or to expose the chest and attach electrodes to it, which makes handling easier, reduces the limitation of the object of use, and eliminates discomfort to the living body. You.

According to the present embodiment, even if the pulse rate PR (t) is weak as shown in FIG.
Has the advantage that it can be detected accurately.

Next, an embodiment of the second invention will be described. In the following embodiment, since the respiratory rate RR is measured based on the change in the waveform of the pulse wave signal SM, the hardware configuration is the same as that shown in FIG. Portions common to the embodiments are denoted by the same reference numerals, and description thereof is omitted.

FIG. 7 is a functional block diagram for explaining the function of this embodiment. In the figure, a pulse wave signal SM synchronized with a heartbeat is output from a pulse wave detecting means 50 corresponding to the pulse wave sensor 10. The pulse wave shape change detecting means 52 detects a periodic change in the shape of the pressure pulse wave detected by the pulse wave detecting means 50, and the respiratory rate calculating means 54 detects the pulse wave shape change detecting means 52. The respiratory rate RR of the living body is calculated according to the shape change cycle of the pressure pulse wave.

The operation of the measuring circuit 14 of this embodiment will be described with reference to the flowchart shown in FIG. First, step S
In F1, it is determined whether a pulse wave for one cycle has been input. If the determination in step SF1 is denied, there is a case where the change in the pulse wave shape cannot be grasped. Therefore, the process waits until the determination in step SF1 is affirmed.
However, if the determination in step SF1 is affirmed, the magnitude of the pulse wave is normalized in step SF2, and then in step SF3, the main part of the normalized pulse wave shape for one cycle. Is quantified. That is, in step SF3 of the present embodiment, for example, as shown in FIG.
In the pulse wave of one cycle T _M , the area S _M in the period t _L from the maximum peak position to the elapse of a predetermined time, for example, a half cycle (= T _M / 2), is given by the following equation (3). Desired. Since the area S _M is a value that changes with a change in the shape of the pulse wave after the maximum peak position, the area S _M quantitatively represents the pulse wave shape within a predetermined period t _L after the maximum peak position. Quantity.

[0032]

(Equation 5)

[0033] In step SF4, the change period T _F of the area S _M showing the quantification pulse wave shape for each pulse wave is determined. Then, in step SF5, the respiratory rate RR is calculated based on the change period T _F from the following equation ( 4 ), and the value of the respiratory rate RR is displayed on the display 28. Of the shape of the pulse wave, the shape of the maximum peak position after whereas a deep portion of the correlation with the respiration rate of a living body, the area S _M is in accordance with the change of the maximum peak position after the shape of the pulse wave change Therefore, the respiration rate RR can be determined based on the change in the area S _M. here,
In the following equation (4), T _Fn-3 is the cycle obtained in the previous three cycles, T _Fn-2 is the cycle obtained in the two previous cycles, and T _Fn-1 is obtained in the previous cycle. It is a cycle. In the present embodiment, the above steps SF3 and SF
4 corresponds to the pulse wave shape change detecting means 52, and step SF
5 corresponds to the respiratory rate calculating means 54.

[0034]

(Equation 6)

Also in this embodiment, since the pulse wave sensor 10 need only be attached to the wrist when measuring the respiratory rate, the temperature sensor is attached to the nose of the living body with a clip, or a rubber tube is wound around the chest. Alternatively, since it is not necessary to expose the chest and attach an electrode thereto, the handling is simplified, the number of objects to be used is reduced, and discomfort to the living body is eliminated. Further, according to the present embodiment, the magnitude of the pulse wave is normalized in step SF2, so that the influence of the variation in SYS is removed, and the area S _M calculated in step SF3 is an area above 0 _mm Hg. Therefore, the influence of the variation in DIA is eliminated, and the area S _M calculated in step SF3 becomes equal to the predetermined period t.
_Since the area is within _L , there is an advantage that the influence of variation in PR is removed.

Next, still another embodiment of the present invention will be described. In step SF3 of the embodiment of FIG. 8 described above, the area S _M obtained from Expression (3) is used as a value quantitatively representing the shape of the pulse wave in a portion closely related to the respiratory rate. following formula (5) may be used weighted area S _MO obtained from. Thus, since the burden as the rear end of the period t _L is increased, also the area S _M is the same as for the pulse wave waveform shown in solid and dashed lines is reversed in FIG. 10, according to the weighted area S _MO If the shape can be identified. According to the present embodiment, in addition to the effects of the embodiment shown in FIG. 8, as shown in FIG. 11, the upper peak clearly appears as compared with the N-PRP of the above-described embodiment, so that the respiratory rate Measurement accuracy is obtained.
Further, according to the present embodiment, there is an advantage that the shape change is accurately represented even if the waveform after the upper peak of the pulse wave is reversed.

[0037]

(Equation 7)

Another embodiment of the present invention will be described. In step SF3 of the above-described embodiment, the area S _M or S _MO shown in FIG. 9 is used as a quantity quantitatively representing the shape of the pulse wave, and the respiration rate RR is measured according to the periodic change. As illustrated in FIG. 12, a triangular shape connecting point A, which is the upper peak of the pulse wave, point B, which has passed 1/4 cycle from point A, and point C, which has passed 1/2 cycle from point A, The area F may be used. FIG. 13 shows another example that replaces steps SF3 and SF4 in FIG.

In FIG. 13, when the input of one pulse wave is determined and its normalization processing is completed, in step SG1, the upper peak of the pulse wave at point A, Three points are determined: a point B and a point C on a pulse wave that has elapsed from the point A by a half cycle. Next step SG
In 2, the value at the point B (the magnitude of the pulse wave at the point B: pressure value)
And the value at point C (the magnitude of the pulse wave at point C: pressure value) are compared with each other to determine whether they are equal to each other and which value is greater.

If the input pulse wave has the shape shown in FIG. 12, it is determined in step SG2 that the value at point B is greater than the value at point C. The calculation formula (6) or the first map corresponding thereto is used. However, if the input pulse wave has the shape shown in FIG. 14, it is determined in step SG2 that the value at point B and the value at point C are the same. The area calculation formula (7) or the corresponding second map is used.
When the input pulse wave has the shape shown in FIG. 15, the value of point B is determined to be smaller than the value of point C in step SG2, and the third area shown in the following equation is determined in step SG5. Calculation formula (8) or the third formula corresponding thereto
Maps are adopted.

The first area calculation formula (6) is derived so as to represent the area F of the triangle ABC in FIG. 16 in consideration of the condition that a '= b'. The second area calculation equation (7) is derived in FIG. 17 so as to represent the area F of the triangle ABC in consideration of the conditions of a ′ = b ′ and a ″ = c ″. The third area calculation formula (8) is derived in FIG. 18 so as to represent the area F of the triangle ABC in consideration of the condition that a ′ = b ′. Area F to see periodic changes
When the relative comparison is made, those equations (6),
The coefficient (a '/ 2) on the right side of (7) and (8) may be removed. Also, instead of the normalization processing in step SF2,
The right side of the equations (6), (7) and (8) may be multiplied by c ″.

[0042]

(Equation 8)

[0043]

(Equation 9)

[0044]

(Equation 10)

In step SG6, the area F is sequentially calculated for each pulse wave from the area calculation formula adopted as described above, and in step SG7, the change period T _F of each area _F is determined. In the following step SF5, the respiration rate RR is calculated from the previous equation (4) based on the change period T _F.

In this embodiment, step SG1
SG7 correspond to the pulse wave shape change detecting means 52, and the same effect as the embodiment shown in FIG. 8 can be obtained. Further, in the present embodiment, there is an advantage that the area calculation formula is automatically selected according to the shape of the pulse wave SM. The basic shape of the pulse wave is
The same area calculation formula is used during the measurement because it changes depending on the individual difference and the mounting position of the pulse wave sensor 10.

Although the embodiment of the present invention has been described in detail with reference to the drawings, the present invention can be applied to other embodiments.

For example, in the embodiment of FIG.
Although a common pulse wave sensor 10 has been used to obtain a pulse rate and a systolic blood pressure value, a photoelectric pulse for extracting a photoelectric pulse wave, which is a pulsation of transmitted light or reflected light, at a peripheral portion of a living body such as a finger, an earlobe, or skin. A sensor, an impedance pulse wave sensor attached to the impedance pulse wave, which is a change in the impedance of the peripheral portion, and a pulse wave, which is a pulse flow in the artery in the peripheral portion or a change in the arterial wall, which is extracted using ultrasonic waves. An acoustic pulse wave sensor or the like may be used exclusively for detecting the pulse rate independently of the pulse wave sensor 10.

In equation (1) of the embodiment shown in FIG. 2, "2" is used as the number n for reducing the weight of SYS (t). It may be a numerical value.

In the embodiment of FIG. 8, the respiration rate RR is measured based on the change in the shape of the pressure pulse wave detected by the pulse wave sensor 10. The pulse wave may be a photoelectric pulse wave, a fingertip pulse wave, an impedance pulse wave, or a volume pulse wave which is optically and electrically detected from a finger or the like.

Further, the pulse rate detecting means 30 of the above-described embodiment is used.
And the systolic blood pressure value SYS (t) obtained by the systolic blood pressure value detecting means 32
May be a moving average value of several beats before that.

[0052] Further, instead of the second area calculation expression in step SG4 the previous embodiment, by a this inclination of a straight line connecting point A and point C (= 100 × a / c) is used, the pulse wave The shape may be quantified.

[0053] It is to be an example of the last present invention was described above, the present invention various modifications may be added within a range not departing de its gist.

[Brief description of the drawings]

FIG. 1 is a functional block diagram illustrating functions of an embodiment of FIG. 2;

FIG. 2 is a block diagram illustrating a configuration according to an embodiment of the present invention.

FIG. 3 is a diagram showing an example of a pulse wave signal detected by the pulse wave sensor of the embodiment in FIG.

FIG. 4 is a time chart showing an example of changes in pulse rate PR (t), systolic blood pressure value SYS (t), and N-PRP (t) in the embodiment of FIG. 2;

FIG. 5 is a flowchart illustrating the operation of the embodiment in FIG. 2;

6 is a time chart showing changes in pulse rate PR (t), systolic blood pressure value SYS (t), and N-PRP (t) in the embodiment of FIG. Is shown.

FIG. 7 is a functional block diagram for explaining functions of another embodiment of the present invention shown in FIG. 8;

FIG. 8 is a flowchart illustrating the operation of a measurement circuit according to another embodiment of the present invention.

9 is an area S quantitatively representing the pulse wave shape of the embodiment in FIG.
It is a figure explaining _M.

FIG. 10 is a diagram illustrating the operation and effect of the embodiment shown in equation (5).

FIG. 11 is a time chart for explaining the operation and effect of the embodiment shown in equation (5).

FIG. 12 is a diagram illustrating a shape of an area F calculated by a first area calculation formula in the embodiment of FIG.

FIG. 13 is a flowchart illustrating a main part of an operation according to another embodiment of the present invention.

14 is a diagram illustrating a shape of an area F calculated by a second area calculation formula of the embodiment in FIG.

15 is a diagram illustrating a shape of an area F calculated by a third area calculation formula in the embodiment of FIG.

FIG. 16 is a diagram illustrating a first area calculation formula of the embodiment in FIG.

FIG. 17 is a diagram illustrating a second area calculation formula in the embodiment of FIG.

FIG. 18 is a diagram illustrating a third area calculation formula of the embodiment in FIG.

[Explanation of symbols]

 10: pulse wave sensor 30: pulse rate detecting means 32: systolic blood pressure value detecting means 34: N-PRP calculating means 36: respiratory rate calculating means 50: pulse wave detecting means 52: pulse wave shape change detecting means 54: respiratory rate calculating means

Continuation of the front page (56) References JP-A-4-53534 (JP, A) JP-A-59-189832 (JP, A) JP-A-62-22627 (JP, A) JP-A-2-121006 (JP) , U) Japanese Utility Model Application Hei 2-121007 (JP, U) Japanese Utility Model Application Hei 1-65007 (JP, U) Japanese Utility Model Application Hei 4-51912 (JP, U) (58) Fields surveyed (Int. Cl. ⁷ , DB A61B 5/08 A61B 5/022 A61B 5/0245

Claims (3)

(57) [Claims] An apparatus for measuring a respiratory rate of a living body, comprising: a pulse rate detecting section for sequentially obtaining a pulse rate of the living body from a pulse wave continuously generated from a peripheral portion of the living body in synchronization with a heartbeat. Means, a systolic blood pressure value detecting means for sequentially obtaining a systolic blood pressure value of the living body from a magnitude of a pressure pulse wave continuously generated in synchronization with a heartbeat from an artery of a limb of the living body, and the pulse rate and systolic blood pressure A respiratory rate calculating means for calculating a multiplied value of the value; and a respiratory rate calculating means for calculating a respiratory rate of the living body according to a pulsation cycle of the multiplied value calculated by the multiplied value calculating means. Number measuring device. 2. The multiplication value calculation means, wherein the pulse rate obtained by the pulse rate detection means is PR (t), and the systolic blood pressure value obtained by the systolic blood pressure value detection means is SYS (t). The respiratory rate measuring device according to claim 1, wherein the multiplication value N-PRP (t) is calculated according to the following equation. ( Equation 1 ) N-PRP (t) = PR (t) × [SYS (ti) / n] (where n is a number greater than 1 and i is PR (t) and SYS)
phase difference from (t)) 3. An apparatus for measuring a respiratory rate of a living body, comprising: a pulse wave detecting means for sequentially detecting a pulse wave continuously generated in synchronization with a heartbeat of the living body; Its maximum in the detected pulse wave
Obtain the area of a predetermined time zone that elapses from the peak position,
Pulse wave shape change detecting means for detecting a change in the shape of the pulse wave by area ; respiratory rate calculating means for calculating a respiratory rate of the living body in accordance with a pulse wave shape change cycle detected by the pulse wave shape change detecting means; A respiratory rate measuring device comprising: