DE69835843T2 - Pulse wave examination apparatus - Google Patents

Description

technical area

The The present invention relates to a device for pulse wave examination, which is suitable for specifying the type of human pulse wave is a blood pressure monitor that measures the mean blood pressure and pulse pressure used as a parameter, and a pulse waveform monitor and a pharmacological impact monitor that use a parameter referring to a dicrotic notch portion of an arterial pressure waveform refers.

State of technology

The Pulse wave is for usually defined as a wave of blood that is emitted from the heart and to propagate through a blood vessel. For this reason it is known that various types of medical Information by detecting the pulse wave and the analysis of the detected pulse wave can be obtained. Ongoing studies at the pulse wave have shown that different types of information, which are only obtained from the blood pressure and the pulse rate can, by analyzing the pulse wave captured by the human body is, by different techniques can be obtained by a diagnosis based on these types of information becomes possible.

The Inventors of the present invention have found in PCT / JP96 / 01254 (Title of the invention: DIAGNOSTIC APPARATUS FOR DETECTING CONDITION OF LIVING BODY AND CONTROLLER) the ratio between the pulse waveform and their rate of distortion and made possible the diagnosis of body condition a person by detecting and treating the pulse waveform of the Person by calculating the distortion rate of the waveform and the Waveform was specified from the distortion rate.

Here will the ratio between a pulse waveform and a distortion rate, which in mentioned in the above application are briefly described.

First, there are various types of pulse waveforms and the forms are diversified. Here are typical forms of pulse waveforms described by the classification of Chinese medicine, which is a traditional oriental medicine. 45A to 45C are diagrams showing representative pulse waveforms by this classification.

In the 45A The pulse waveform shown is called "ping mai," and is the body state of a normal person of good health. "Ping mai" is characterized in that, as shown in the figure, the pulse is relaxed and has a constant rhythm without interruption.

Second, the pulse waveform used in 45B is shown as "Hua mai" indicative of the pulse state of a human having an abnormality in its bloodstream state. The wave form of Hua mai shows a sharp, rapid rise, and then drops abruptly, with the aortic dicrotic notch deep, while the following peak is significantly higher than that of Ping mai. It is believed that diseases such as breast cancer, liver or kidney disease, respiratory problems, stomach or intestinal disease or inflammation, or some other diseases cause the movement of the blood to be very fluid and even, creating "Hua mai".

Further, the pulse waveform that is in 45C shown as "Xuan may" indicating the pulse state of a human whose blood vessel wall tension has increased. Xuan may is characterized by its waveform rising sharply and remaining in a high pressure state for a certain period of time without immediate drop. "Xuan may" is observed in diseases such as liver and gallbladder disease, dermatological conditions, high blood pressure and pain. It is believed that the tension in the automatic nervous system causes contraction of the walls of the blood vessels, thereby decreasing the elasticity, so that the effect of the blood pulsation of the pumped blood is not simply expressed, thereby causing this phenomenon.

The ordinate and abscissa in the graphics of 45A to 45C show the blood pressure (mmHg) or the time (seconds).

wobei A₁ die Amplitude einer Grundwellenkomponente in der Pulswelle ist und A₂, A₃, ..., A_n die Amplituden der zweiten, dritten, ..., beziehungsweise n-ten harmonischen Komponente sind.The relationship between the pulse state of the pulse waveform and its distortion rate d is in 46 shown. Here, the distortion rate d of the pulse waveform will be expressed by the following equation (1) Right:

where A _{1 is} the amplitude of a fundamental wave component in the pulse wave and A ₂ , A ₃ , ..., A _{n are} the amplitudes of the second, third, ..., and n-th harmonic components, respectively.

It is therefore possible to quantitatively specify the pulse state of the pulse waveform from the correlation shown in FIG 46 is shown when the pulse waveform of a person is detected and the detected waveform is subjected to FFT (Fourier Transform) treatment to obtain the amplitudes A ₁ to A _n from which the distortion rate d is calculated.

If, as in 46 is shown, the pulse state of the person is judged as Hua mai, the distortion rate d is in the range between 0.98 and 1.22. If the pulse state is judged to be Pingmai, the distortion rate d is in the range of 0.92 to 1.10. When the pulse state is judged to be Xuan may, the distortion rate d is in the range of 0.73 to 0.94.

In In this case, the pulse state can be judged as Hua mai or Ping mai when the distortion rate d of the pulse waveform is in the range between 0.98 and 1.10. Likewise, the pulse state as Ping May or Xuan may be judged when the distortion rate d of Pulse waveform is in the range between 0.92 and 0.94. It is therefore difficult, the pulse state by a conventional device for pulse wave examination precise to determine.

by the way Will be a blood pressure monitor that has a maximum blood pressure and measures a minimum blood pressure and displays these pressure values, used for non-invasive blood pressure recording.

Even though the maximum blood pressure or minimum pressure of persons are the same There are different types of waveforms for blood pressure. Thus are the characteristics of the blood pressure of a person inadequate, though They only by a maximum blood pressure and a minimum blood pressure expressed become.

Of the Mean blood pressure is an important parameter to the condition of the patient To experience a person's blood pressure. The mean blood pressure can not just by measuring maximum blood pressure and a minimum Blood pressure can be obtained.

In Pulse detection used in Chinese medicine or traditional Indian medicine is being applied, will be a medical examination by testing the pulse waveform is executed, which is detected with the fingers when using a medical examiner optimal pressing force to a distal position of the forearm of the radial artery compresses, that is, a medical examination is carried out, by detecting a fluctuation with the pressing force, wherein the medical examiners the fluctuation in the fingers feels which corresponds to a fluctuation in blood pressure.

In For example, Chinese medicine uses the pulse waveform, the when applying an adequate pressing force to the radial artery felt is broadly divided into three categories, which as previously mentioned are referred to as "Ping mai", "Hua mai" and "Xuan mai" respectively. Ping Mai is calm and gentle, and the rhythm is stable and poor at turbulence. Ping mai is a pulse pattern for a person of good health. Hua mai is the kind where the flow of the pulse is very fluid and felt evenly , and indicates an abnormality in the bloodstream condition. Xuan Mai is perceived as a straight, firm and long pulse and is attributed to a tension or aging of a blood vessel wall.

One however, such medical examination method depends on the pulse waveform which is classified by the medical examiner's sense of what Problems regarding objectivity and reproducibility arise.

The The present invention has been made in view of the above situation made and its task is to provide a pulse wave examination, which can assess the pulse state objectively and accurately.

Another object of the present invention is to provide a blood pressure monitor that can more accurately monitor the blood condition than maximum and minimum blood pressure information and that non-invasively monitor the monitoring parameters that characterize blood pressure can.

A Another object of the present invention is the provision of a pulse waveform monitor performing an examination with the aid of Pulse waveform can perform objectively and reproducibly.

US U.S. Patent No. 5,027,641A discloses an oscillometric, non-invasive Blood pressure simulator enabling the testing of oscillometers without disassembling or otherwise affecting the oscillometer. For the simulator to work, tests were run to Capture waveforms of multiple users who are representative of it are what an oscillometric blood pressure monitor detects. The direct Arterial pressure was from the left radial artery and the aorta recorded. Then the users got a catheter and the stability every pressure signal was checked. Then a test inflation cycle was initiated and the oscillometer became to check the stability and quality the two indirect pressure signals used. The data was then analyzed the topical characteristics of the pulse waveform and oscillometric envelope identify each user. The analyzed pulse wave properties were the width and the duty cycle, the rise time, fall time, Energy, maximum and minimum slope and waveform indices. One Note for the general similarity of waveforms at various mean cuff pressures by calculating the autocorrelation function (ACF) of the pulse waveform for one get certain user as a single data acquisition cycle. There the device has a physiologically correct pulse waveform and oscillometric envelopes (derived from the testing) is a valid test any oscillometric monitor possible regardless of the special method used to determine systolic and diastolic pressures is used.

The International Patent Publication No. 97 / 24982A discloses a method and a device for measurement of cardiac output. The arterial blood pressure of a user becomes continuously monitored. The Output data from the monitor is amplified and smoothed to to obtain a continuous blood pressure waveform. The waveform is then subjected to a non-linear transformation, which is the Variations in the characteristics of the arterial system with pressure corrected. The corrected waveform then becomes an autocorrelation subjected to the pulsatility and derive the heart rate of the corrected waveform. The nominal Stroke volume is calculated from the pulsatility and the nominal Cardiac output is multiplied by multiplying the nominal stroke volume with the heart rate received.

epiphany the invention

• (1) A device for pulse wave examination according to the present The invention comprises a pulse wave detection means for detecting a Pulse waveform from the detection position of a living body; one Autocorrelation calculation means for calculating autocorrelation data, indicating the autocorrelation of the pulse waveform produced by the Pulse wave detection means is detected; and a pulse state data extracting means for obtaining pulse state data representing the type of pulse waveform indicate based on the autocorrelation data; and where that Pulse state data acquisition means, the pulse state data by comparing the autocorrelation data with a prescribed threshold generated.
• (2) In the pulse wave examination apparatus as shown in Item (1) preferably includes the pulse state data extraction means a minimum value detecting section for detecting the minimum value the autocorrelation data currency end a period of a heartbeat, as well as a comparison section for comparing the minimum value obtained from the minimum value detection section is detected, with the threshold value, to the pulse state data win.
• (3) In the pulse wave examination apparatus as in Item (1) preferably includes the pulse state data extraction means a minimum value detecting section for detecting an average minimum value by averaging each minimum value of the autocorrelation data, which are detected in each of the several heartbeat periods, as well a comparison section for comparing the average one Minimum value detected by the minimum value detection section is, with the threshold, to gain the pulse state data.
• (4) In the pulse wave examination apparatus as in Item (1) preferably includes the pulse state data extracting means: a timing section for comparing the autocorrelation data with the threshold to measure a time interval in which the Autocorrelation data exceeds or falls below the threshold; a calculating section for calculating the ratio the time interval measured by the time measuring section with a period of a heartbeat; and a comparison section for comparing the result obtained by the calculating section is calculated with a prescribed threshold to the To gain pulse state data.
• (5) In the pulse wave examination apparatus as in item (4), the calculating section calculates Preferably, the ratio of the time interval measured by the time measuring section to a period of a heartbeat and calculates the average of the calculated results.
• (6) In the device for pulse wave examination as under Item (1) preferably includes the pulse state data extraction means a change rate calculating section to record the rate of change the autocorrelation data based on the autocorrelation data, and a change rate comparison section for comparing the rate of change, which is detected by the change rate calculation section is, with the threshold, to gain the pulse state data.
• (7) In the pulse wave examination apparatus as shown in Point (6) detects the change rate comparison section preferably a maximum value of the rate of change, and compares the maximum value of the rate of change with the threshold value to obtain the pulse state data.
• (8) In the pulse wave examination apparatus as in Item (1) preferably includes the pulse state data extracting means: a minimum value detecting section for detecting the minimum value the autocorrelation data during a period of a heartbeat; a first comparison section for comparing the minimum value obtained from the minimum value detection section with a prescribed first threshold To gain heart rate data indicating a Xuan may, if the minimum value is less than the first threshold; one Timing section for comparing the autocorrelation data with a prescribed second threshold, at a time interval in which the autocorrelation data exceeds the threshold or fall short of; a calculating section for calculating the ratio the time interval measured by the time measuring section with a period of a heartbeat; and a second comparison section for comparing the result obtained by the calculating section is calculated, with a prescribed third threshold, to gain the pulse state data that may be a ping mai or a Show Hua Mai.
• (9) In the device for pulse wave examination as under Item (1) preferably includes the pulse state data extracting means: a minimum value detecting section for detecting the minimum value the autocorrelation data during a period of a heartbeat; a first comparison section for comparing the minimum value obtained from the minimum value detection section with a prescribed first threshold To gain heart rate data indicating a Xuan may, if the minimum value is less than the first threshold; one Variation calculation section for detecting a rate of change the autocorrelation data based on the autocorrelation data; and a second comparison section for comparing the rate of change, that of the rate of change calculation section calculated with a prescribed second threshold, to gain the pulse state data that may or may not be a ping Show Hua Mai.
• (10) In the pulse wave examination apparatus as in Point (8) or (9), the autocorrelation data is preferably one Coefficient of autocorrelation, and the first threshold, the in the comparison operation used in the first comparison section accomplished is about 0.25.
• (11) In the pulse wave examination apparatus as in At point (8), the auto-correlation data is preferably a coefficient the autocorrelation, and the second threshold used in the comparison operation being performed in the time measuring section is designed so that it is in a range between 0.4 and 0.8.
• (12) The device for pulse wave examination as under a of the items (1) to (11) further preferably comprises: a body movement detecting means for capturing the waveform of body movement affecting body movement of the living body displays; and a body movement component eliminating agent for eliminating a body movement component from the pulse waveform to a body motion-eliminated pulse waveform to gain, with the body movement component in the pulse waveform based on the body motion waveform becomes; wherein the autocorrelation computation means autocorrelation data which eliminated autocorrelation based on body movement Specify the pulse waveform instead of the pulse waveform.
• (13) The pulse wave examination device as in point (12) further preferably comprises: a judging means for Judging the presence of body movement of the living body the base of the body motion waveform, that of the body movement detection means is detected, wherein the Körperbewegungskomponenteneliminierungsmittel the body movement eliminating process stops when the assessment means the absence of body movement indicates the pulse waveform instead of the body motion-eliminated pulse waveform issue.
• (14) The pulse wave examination apparatus as in any one of (1) to (11) further preferably comprises: first wavelet transform means for performing wavelet transformation of the pulse waveform detected by the pulse wave detection means to pulse wave analysis data for each frequency zone to win; a body movement detecting means for detecting the movement of the living body to output the waveform of the body movement; second wavelet transform means for performing wavelet transformation of the body motion waveform detected by the body motion detection means to provide body motion analysis data for each frequency zone to win; a body movement component eliminating means for subtracting the body movement analysis data from the pulse wave analysis data to obtain body movement-eliminated pulse wave analysis data; and an inverse wavelet transform means for performing an inverse wavelet transform of the body motion-eliminated pulse wave analysis data to obtain a body motion-eliminated pulse waveform; wherein the autocorrelation calculation means calculates autocorrelation data indicating autocorrelation on the basis of the body movement-eliminated pulse waveform instead of the pulse waveform.
• (15) The device for pulse wave examination as under a of the items (1) to (11) further preferably includes: a wavelet transforming means to run a wavelet transformation of the pulse waveform generated by the pulse wave detection means is detected to obtain pulse wave analysis data for each frequency zone; a body movement component eliminating agent for eliminating a prescribed frequency component, the one body movement corresponds, from the pulse wave analysis data, to body motion-eliminated pulse wave analysis data to win; and an inverse wavelet transform means for To run an inverse wavelet transformation of the body motion-eliminated pulse wave analysis data, by a body movement-eliminated To gain pulse waveform; the autocorrelation computation means Autocorrelation data indicating an autocorrelation on the Base of body movement-eliminated Calculated pulse waveform instead of the pulse waveform.
• (16) The device for pulse wave examination as in point (1) preferably further comprises: a first wavelet transform means to run a wavelet transformation the pulse waveform detected by the pulse wave detecting means to obtain pulse wave analysis data for each frequency zone; and wherein the autocorrelation calculating means is an autocorrelation indicates the pulse wave analysis data in a particular frequency zone.
• (17) The device for pulse wave examination as in point (16) preferably further comprises: a body movement detection means to capture the movement of the living body to the waveform of the body movement to spend; a second wavelet transform means for performing a wavelet transform the waveform of body movement, that of the body movement detection means is recorded to body movement analysis data for every Gain frequency zone; a body movement component eliminating agent for subtracting the body movement analysis data from the pulse wave analysis data to body movement-eliminated To gain pulse wave analysis data; and wherein the autocorrelation calculation means an autocorrelation of the body motion-eliminated pulse wave analysis data indicating in a particular frequency zone.
• (18) The device for pulse wave examination as in point (16) preferably further comprises: a body movement component eliminating agent for eliminating a prescribed frequency component, the one body movement corresponds to body movement-eliminated To gain pulse wave analysis data; and wherein the autocorrelation calculation means an autocorrelation of the body motion-eliminated pulse wave analysis data indicating in a particular frequency zone.
• (19) The device for pulse wave examination as under a of the items (1) to (18) further preferably comprises: notification means for transmission the pulse state data obtained from the pulse state data extracting means be won.

Short description of drawings

1 Fig. 10 is a block diagram showing the structure of a pulse wave examination apparatus of a first embodiment.

2 FIG. 10 is a flowchart for describing the operation of the pulse wave examination apparatus of the first embodiment. FIG.

3 Fig. 10 is a block diagram showing the structure of a pulse wave examination apparatus of a second embodiment.

4 Fig. 10 is a block diagram showing an example of the structure of a wavelet transform section of the second embodiment.

5 Fig. 10 is a block diagram showing the structure of a waveform shaping section of the second embodiment.

6 Fig. 10 is a timing chart showing the operation of the waveform shaping section of the second embodiment.

7 FIG. 14 is a view for describing the operation of a detection element for the tidal wave / dicrotic wave of the second embodiment. FIG.

8th Fig. 12 is a view showing an electrocardiogram of a waveform, a waveform of the arterial pressure, and a waveform of the blood pressure at a peripheral part, which correspond to each other.

9 Fig. 16 is a view for describing the relationship between the pulse waveform and the waveform parameters.

10 Fig. 13 is a view showing the relationship between a difference in blood pressure (y ₅ -y ₄ ) and a distortion rate d.

11 is a view showing the result of a frequency analysis of Hua mai.

12 is a view showing the result of a frequency analysis of Pingmai.

13 is a view showing the result of a frequency analysis of Xuan Mai.

14 is a table showing the amplitudes of a tidal wave and a dicrotic wave for each pulse state.

15 is a table showing a harmonic component of each pulse state.

16 is a view showing an auto-correlation coefficient of Xuan may.

17 is a view showing an auto-correlation coefficient of Pingmai.

18 is a view showing an auto-correlation coefficient of Hua mai.

19 Fig. 10 is a block diagram showing the electrical structure of a pulse wave inspection apparatus of a third embodiment.

20 FIG. 11 is a flowchart showing the operation of the pulse wave inspection apparatus of the third embodiment. FIG.

21 FIG. 12 is a block diagram of a pulse state data extracting section according to a fourth embodiment. FIG.

22 Fig. 13 is a view showing the variation rate in autocorrelation data of a typical pulse waveform.

23 FIG. 10 is a flow chart showing the operation of a pulse wave examination apparatus of the fourth embodiment. FIG.

24 Fig. 10 is a block diagram showing the electrical structure of a pulse wave inspection apparatus of a fifth embodiment.

25 Fig. 10 is a block diagram showing the electrical structure of a pulse wave examination apparatus of a sixth embodiment.

26 Fig. 13 is a view showing pulse wave analysis data during a sub-period in a pulse waveform.

27 FIG. 10 is a timing chart for describing the operation of a body movement eliminating section according to the sixth embodiment. FIG.

28 FIG. 14 is a view showing corrected data MKDa of a pulse wave during the period Tc in the sixth embodiment.

29 FIG. 12 is a view showing corrected body movement data TKDa during the period Tc in FIG sixth embodiment.

30 Fig. 13 is a view showing body movement elimination pulse wave data MKDaj excluding a body movement component in the sixth embodiment.

31 Fig. 10 is a block diagram showing the electrical structure of a pulse wave examination apparatus of a seventh embodiment.

32 Fig. 10 is a block diagram of a body movement eliminating section of the seventh embodiment.

33 Fig. 13 is a view showing an example of body movement-eliminated pulse wave data of the seventh embodiment.

34 Fig. 10 is a block diagram showing the electrical structure of a pulse wave examination apparatus of an eighth embodiment.

35 Fig. 10 is a block diagram of a first wavelet conversion section of the eighth embodiment.

36 Fig. 10 is a block diagram showing the electrical structure of a pulse wave examination apparatus of a ninth embodiment.

37A Fig. 13 is a view showing the state of a built-in pulse wave inspection apparatus such as a wristwatch.

37B Fig. 12 is a view showing a pulse wave detection section of a wristwatch type pulse wave inspection apparatus.

37C Fig. 12 is a view showing a connector portion mounted in the body portion of a wristwatch type pulse wave inspection apparatus.

38 Fig. 13 is a view showing an example of the structure of a pulse wave detection section.

39A Fig. 12 is a view showing the external appearance of a pulse wave examination apparatus when manufactured in a different type of wristwatch.

39B FIG. 14 is a view showing the state of the built-in pulse wave examination apparatus incorporated in FIG 39A is shown.

40 Fig. 13 is a view showing the external appearance of the structure of the pulse wave examination apparatus when made in a kind of necklace.

41 FIG. 14 is a view showing the state in which a pulse wave detection section of FIG 40 shown device for pulse wave examination is attached to the carotid artery.

42 Fig. 13 is a view showing the external appearance of the structure of a pulse wave examination apparatus when it is made in the manner of glasses.

43 Fig. 13 is a view showing the external appearance of the structure of a pulse wave examination apparatus when fabricated in the manner of a card.

44A Fig. 12 is a view showing the external appearance of the structure of a pulse wave examination apparatus when it is manufactured in the manner of a pedometer.

44B FIG. 14 is a view showing the state of the built-in pulse wave examination apparatus incorporated in FIG 44A is shown.

45A is a view showing the pulse waveform of a typical ping mai.

45B is a view showing the pulse waveform of a typical Hua mai.

45C is a view showing the pulse waveform of a typical Xuan may.

46 FIG. 13 is a view showing the relationship between the distortion rate and the pulse waveform. FIG.

47 Fig. 12 is an explanatory view showing a structure used for recording a waveform of arterial pressure in the radial artery to show a theoretical basis for a tenth embodiment.

48 Figure 12 is a graph showing a typical waveform of arterial pressure.

49 is a graph of experimental results obtained using the in 47 were obtained, showing the relationship between the mean blood pressure and the diastolic blood pressure.

50 is a graph of experimental results obtained using the in 47 were obtained, showing the relationship between the mean blood pressure and the systolic blood pressure.

51 is a graph of experimental results obtained using the in 47 structure, which shows the relationship between the pulse pressure and the systolic blood pressure.

52 Fig. 10 is a block diagram showing a blood pressure monitor of a tenth embodiment.

53 Fig. 12 is a graph showing the distribution of the dicrotic wave height ΔBP _D for each pulse waveform to show a theoretical basis for an eleventh embodiment.

54 Fig. 16 is a graph showing the relationship between a dicrotic pressure difference ratio BP _Dd / ΔBP and a dicrotic wave height ΔBP _{D to} show a theoretical basis for an eleventh embodiment.

55 Fig. 12 is a graph showing the relationship between a diastolic ejection pressure ΔBP _P and a dicrotic wave height ΔBP _{D to} show a theoretical basis for an eleventh embodiment.

56 Fig. 10 is a block diagram showing the structure of a pulse waveform monitor of the eleventh embodiment.

57 Fig. 10 is a block diagram showing the structure of a pharmacological performance monitor of the twelfth embodiment.

58 Fig. 10 is a block diagram showing a modification in which a wavelet transform section includes a filter bank.

59 Fig. 10 is a block diagram showing a modification in which an inverse wavelet transform section comprises a filter bank.

60 is a face table showing a modification of a notification.

61 Fig. 10 is a view showing an example of a transmission type photoelectric pulse wave sensor in a modification.

62 Fig. 13 is a view showing a modification in which a photoelectric pulse wave sensor is attached to glasses.

63 Fig. 12 is a graph showing a variation in pressure of each section in the arterial pressure waveform upon administration of a hypotensive agent.

64 is a view showing arterial waveforms before and after administration of a blood pressure kenden means shows.

Best embodiment the invention

1. First embodiment

In The result is a device for pulse wave examination according to a first embodiment described.

1.1. Theoretical basis for the first embodiment

It does not have to be mentioned become that the heart emits blood through repeated contractions and dilatations. Here is the time in which blood enters through a contraction / dilatation causing a cycle to flow from the heart, referred to as "ejection time". If the pulse rate, which is the number of contractions of the heart per unit of time, For example, through training, increased when a catecholamine, e.g. Adrenalin, released with the Result that the ejection time rather short. This implies an increase in the force of contraction of the heart muscle.

at an elevated one ejection time The delivery of blood through the contraction / dilatation in one tends Cycle to a rise.

If By the way, it is a person training necessary, the heart muscle, skeletal muscle and the like much oxygen supply, and thus increased the product of pulse rate and output, that is, the Blood flow rate (per unit of time) that is expelled from the heart. As a result of the increased pulse rate is the ejection time short and the tax low. However, because the rate of increase in the pulse rate exceeds the rate of decrease in delivery, the product of pulse rate and total delivery is increased.

Next follows a description of the relationship between the movement of the heart and the waveform of the blood pressure. In the electrocardiogram, which in 8th is shown, the period from the R point to the end point U of the T wave is generally referred to as "ventricular systole", which corresponds to the previous ejection time. The period from the U point to the next R point is referred to as "ventricular diastole". In ventricular systole, ventricular contraction does not occur uniformly, but continues slowly as it spreads from outside to inside. Thus, the waveform of the blood pressure at the proximal portion of an aorta in the ventricular systole ranging from opening to closing of the aortic valve has an upwardly convex shape, as in FIG 8th is shown.

The waveform of the blood pressure at the periphery (radial artery) corresponding to such a blood waveform at the proximal portion of an aorta, that is, the pulse waveform at the periphery is as in FIG 8th shown. The reason why such a waveform forms is presumably that a first wave, referred to as the "ejection wave", occurs as a result of the expulsion of the blood from the heart, a second wave, referred to as the "tidal wave", subsequently due to a reflex at bifurcations of the blood vessel near the heart, and a third wave called the "dicrotic wave" then occurs due to the appearance of a dicrotic notch simultaneous with the closing of the aortic valve.

In the pulse waveform therefore corresponds to the range from the point to the blood pressure reaches a minimum, up to the dicrotic notch the ventricular Systole, and the area from the dicrotic notch to the Point at which the blood pressure reaches a minimum in the next cycle corresponds ventricular diastole.

Here is the point of opening corresponds to the aortic valve in the pulse waveform, the minimum minimum point of blood pressure. Likewise, the point, especially the dicrotic notch, the closing of the Aortic valve corresponds to the third minimum point of the minimum Minimum point, considered in the time series, and the second minimum point from the minimum minimum point, the size of the blood pressure.

Incidentally, the waveform of the peripheral blood pressure in 8th in fact, the pulse waveform, in fact, has a time delay with respect to the waveform of the aortic blood pressure. In the figure, however, this time delay is neglected for the sake of simplicity, and these phases are made equal.

Subsequently, will the waveform of peripheral blood pressure, that is, the Pulse waveform discussed. The pulse waveform at the peripheries a person is detected is the so-called pattern of pressure wave of blood that propagates through a closed system, the from the heart as a pulsating pump and the circulatory system exists as a management. Thus, the pulse waveform is first through regulates the pumping function of the heart, that is, by the state of a Heart function. Second, the pulse waveform is, for example, through the diameter of a blood vessel that Contraction / dilation of a blood vessel and viscous resistance influenced by blood. It is assumed that when the pulse waveform for Analysis is captured, the condition of the person's heart function, such as also the aortic state of the person can be evaluated. This makes understandable that specialists in oriental medicine have a body condition diagnose by the characteristics of the pulsation.

It Now follows a discussion in which a part in the pulse waveform is analyzed.

• (1) eine Zeit t₆ zwischen einem Spitzenpunkt P0 (dem minimalen Minimalpunkt) der ansteigenden Flanke eines Schlages, wobei an dem Punkt der Blutdruckwert in der Pulswellenform ein Minimum erreicht, und einem Spitzenpunkt P6 der ansteigenden Flanke des nächsten Pulses;
• (2) die Werte des Blutdrucks (Differenz) y₁ bis y₅ an Spitzenpunkten (Maximalpunkte und Minimalpunkte), die sequenziell in der Pulswellenform erscheinen; und
• (3) Zeitperioden t₁ bis t₅ vom Spitzenpunkt P0 (dem minimalen Minimalpunkt) beim Pulswellenanfangspunkt bis zu dem Punkt, an dem jeweils jeder der Spitzenpunkte P1 bis P5 erscheint.

First, the inventors of the present invention chose the in 9 represented parameters as those which determine the characteristics of the pulse waveform. In particular, the selected parameters are as follows:

• (1) a time t ₆ between a peak point P0 (the minimum minimum point) of the rising edge of a beat, at which point the blood pressure value in the pulse waveform reaches a minimum, and a peak point P6 of the rising edge of the next pulse;
• (2) the values of the blood pressure (difference) y ₁ to y ₅ at peak points (maximum points and minimum points) appearing sequentially in the pulse waveform; and
• (3) Time periods t ₁ to t ₅ from the peak point P0 (the minimum minimum point) at the pulse wave start point to the point where each of the peak points P1 to P5 appears, respectively.

In this case, each of y ₁ to y ₅ denotes a relative blood pressure value by setting the blood pressure value at a peak point P0 as a given size.

The In fact, inventors of the present invention have recognized Pulse waves of 74 healthy adults between the ages of 22 and 46 years. The waveform parameters of these pulse waves were calculated while each pulse waveform of an FFT treatment as in the aforementioned PCT / JP96 / 01254, was subjected to the distortion rate d of the pulse waveform below Use of the foregoing equation (1) to calculate.

Then, the inventors of the present invention separately examined the correlation between the calculated distortion rate d and each waveform parameter or the differences between these parameters. Thus, it was clarified that the distortion rate d had a high correlation with the pressure differences (y ₅ -y ₄ ) in the blood pressure values, the difference being the amplitude of a dicrotic wave from the dicrotic notch, with a correlation coefficient (R ² ) of 0, 77th This correlation is in 10 shown.

by virtue of this fact led the inventors of the present invention carried out the following analysis the hypothesis that specialists in oriental medicine Feel the features of the dicrotic wave and the tidal wave to to diagnose the pulse state.

In this analysis, each pulse waveform used by specialists in oriental medicine for evaluating the pulse state was subjected to FFT treatment for calculating the ratio of each harmonic component to a fundamental wave component. 11 . 12 and 13 show the results of the analysis of Hua Mai, Ping Mai and Xuan Mai.

In 11 to 13 f1, f2, f3, ..., f10 indicate the amplitudes and phases of a fundamental, second harmonic, third harmonic, ..., and tenth harmonic, respectively. The waveform wf1 is the sum of the fundamental wave f1 and the second harmonic f2, the waveform wf2 is the sum of the fundamental wave f1 to the third harmonic,..., And the waveform wf9 is the sum of the fundamental wave f1 to the tenth harmonic f10.

Here, by comparing the original waveform, the in 11 whose pulse state has been judged by a specialist to be Hua mai, with the original waveform in 12 understand that both are very similar to each other, but the height of the dicrotic indentation is lower at Hua mai than at Ping mai, and the amplitude of the dicrotic wave is larger at Ping mai than at Hua Mai. When the synthesized waveform is observed, it is clear that each original waveform of the dicrotic waves of a Hua mai and Ping may be approximately reproduced by the waveform wf3, which is the sum of the fundamental wave f1 to the fourth harmonic f4.

On the other hand, at Xuan Mai, as in 13 4, it can be seen that the original waveform of the tidal wave is approximately reproduced by the waveform f6 which is the sum of the fundamental wave f1 to the seventh harmonic f7.

14 FIG. 12 shows the amplitudes of the dicrotic wave and the tidal wave in the pulse waveform, representing the pulse state that is in. FIG 11 to 13 is described. The amplitudes of the dicrotic waves are relatively high at 7.3 mmHg and 10.6 mmHg at Hua mai and Ping mai respectively, while the amplitude of the dicrotic wave at Xuan may only be 2.9 mmHg. The amplitudes of the tidal waves in Hua mai and Ping mai are 0, while the amplitude of the tidal wave in Xuan may be 3.8 mmHg.

by virtue of These facts are specific to every dicrotic wave in Huaai and Ping Mai Properties that are in the fundamental f1 to the fourth harmonic f4 are observed. In Xuan Mai, the tidal wave has specific Characteristics observed in high frequency components e.g. in the fifth Harmonic f5 to the seventh harmonic f7.

15 then shows the percentage ratio of the amplitude of each harmonic to the amplitude of the fundamental for each pulse state. Here, if the ratio of the sum of the second harmonic f2, the third harmonic f3, and the fourth harmonic f4 to the fundamental wave f1 is considered in terms of amplitude, that is, (f2 + f3 + f4) / f1, this is 1.74 at Hua May and 1.5 at Ping Mai. It is therefore possible to distinguish between Hua mai and Ping mai on the basis of these values. If the ratio of the sum of the fifth harmonic f5, the sixth harmonic f6 and the seventh harmonic f7 to the fundamental wave f1 is considered in terms of amplitude, that is (f5 + f6 + f7) / f1, this is 0.36 at Hua mai , 0.26 at Ping Mai and 0.42 at Xuan Mai. It is therefore possible to distinguish between Xuan may and other pulses based on these values.

1.2. Structure of the device for pulse wave examination

The Apparatus for pulse wave examination according to this embodiment is based on the theoretical basis described above constructed. In the device for pulse wave examination be the pulse waveforms detected by persons through frequency analysis treated to a tidal wave component and a dikrote Wellenkom component to extract, reducing the pulse state based on the results this extraction is judged. By the way, the outer structure becomes the device for pulse wave examination later in the section "10. External Structures the above-mentioned embodiments "described.

1 Fig. 10 is a block diagram showing the functional structure of the pulse wave examination apparatus according to this embodiment. In this figure, a pulse wave detection section detects 10 the pulse waveform of, for example, the periphery (eg, radial artery) of a person to apply the detected signal as MH to a body movement eliminating section 30 issue.

A body movement detection section 20 For example, it includes an acceleration sensor and detects a person's body movement to apply the detected signal as a TH signal to a waveform treatment section 21 issue. The waveform treatment section 21 For example, it includes a low-pass filter, and performs waveform shaping treatment of the TH signal received from the body motion detection section 20 is output to output a MHt signal showing a body movement component. The body movement eliminator 30 subtracts the MHt signal showing a body movement component from the MH signal received from the pulse wave detection section 10 is output to output a MHj signal showing a pulse wave component.

The pulse wave examination apparatus according to this embodiment is of a type that deals with the pulse waveform detected by a person. In general, in addition to the MHj signal showing a pulse wave component, when the person himself performs some movement, the MHt signal showing a body movement component is superposed on the MH signal received from the pulse wave detection section 10 is detected. Therefore, MH = MHt + MHj and thus the MH signal obtained from the pulse wave detection section 10 is output, not the exact pulse waveform of the person.

There The bloodstream, for example, is influenced by blood vessels and organizations will, by the way, the Body motion component MHt contained in the MH signal, not only as a TH signal considered that the body movement shows the person, but considered as something muted.

Therefore, the body movement eliminator uses 30 as MHt signal, a signal obtained by shaping the waveform of the TH signal in the waveform treatment section 21 is produced. The TH signal directly indicates the person's body movement and is from the body movement detection section 20 output. The body movement eliminator 30 subtracts the MHt signal from the MH signal received from the pulse wave detection section 10 is output to eliminate the influence of the body movement, thereby outputting the MHj signal showing the pulse component. The type, number of stages, constant, and the like of the low-pass filter included in the waveform treatment section 21 are determined on the basis of the data measured in practice.

When the body movement eliminator 30 Incidentally, for the elimination of the body movement component, even if there is no body movement, the noise of the body movement detection section operates 20 a deterioration of the S / N ratio of the signal received from the body movement component eliminating section 30 is output, and energy is consumed by the body movement elimination process. Thus, in this embodiment, a judging section 22 provided. The appraisal section 22 determines whether there is body motion or not based on the body movement waveform TH to provide a control signal C. In particular, the judging section falls 22 a judgment based on a comparison of a threshold with the body movement waveform TH. The threshold is set in advance, taking into account a noise level, so that it can be determined whether the body movement exists or not. Then, when the control signal C indicates that there is no body movement, the operation of the waveform treatment section becomes 21 and the body movement component eliminating section 30 interrupted. In this case, the pulse waveform MH directly from the Körperbewegungskomponenteneliminierabschnitt 30 output. This can be the SN ratio of the output signal from the Körperbewegungskomponenteneliminierabschnitt 30 improve and reduce the energy consumption in the device.

Subsequently, an FFT treatment section undergoes 40 the MHj signal showing a pulse wave component of an FFT treatment to perform a frequency analysis of the pulse wave component. The result of the frequency analysis can be obtained in the form of a plurality of line spectra. Then the frequency and the energy level of each line spectrum are calculated. The FFT treatment section 40 compares this spectrum data and specifies those with the highest energy level as the fundamental wave f1 of the pulse wave component. The FFT treatment section 40 also multiplies the frequency of the fundamental wave f1 in integer to specify each harmonic, and outputs pulse wave analysis data MKD showing each energy level of the fundamental wave f1 and the second harmonic f2 to the tenth harmonic f10.

An extracting section for the tidal wave property 50 then obtains tidal wave characteristic data TWD showing the properties of the tidal wave based on the pulse wave analysis data MKD. As explained above, the properties of the tidal wave can be represented by the ratio of the sum of the fifth harmonic f5, the sixth harmonic f6 and the seventh harmonic f7 to the fundamental wave f1 in the pulse waveform. Thus, the tidal wave characteristic extracting section detects 50 the tidal wave characteristic data TWD according to the following equation: TWD = (f5 + f6 + f7) / f1

Then, an extracting section detects the dicrotic wave property 60 dicrotic wave property data DWD showing the characteristics of the dicrotic wave. As explained above, the characteristics of the dicot wave can be represented by the ratio of the sum of the second harmonic f2, the third harmonic f3 and the fourth harmonic f4 to the fundamental wave f1 in the pulse waveform. Thus, the extracting section detects the dicrotic wave property 60 the dicrotic wave data DWD according to the following equation: DWD = (f2 + f3 + f4) / f1

Then, a pulse state judging section judges 70 the pulse state based on the tidal wave characteristic data TWD and the dicrotic wave characteristic data DWD to obtain pulse state data ZD showing the kind of pulse state of the person. More specifically, the pulse state judgment section compares 70 First, the tidal wave characteristic data TWD having a first threshold to obtain pulse state data ZD1 showing that the pulse state Xuan may be when the tidal wave characteristic data TWD exceeds the first threshold. The first threshold is set in advance so that it is determined whether or not the tidal wave characteristics data TWD Xuan may be. In this example, the first threshold is defined as 0.41.

If the tidal wave property data TWD in contrast to the first threshold become the dicrotic wave property data DWD compared to a second threshold. If the dicrotic Wave property data DWD are below the second threshold, pulse state data ZD2 are determined, which show that the pulse state Ping Mai is while, if the dicrotic wave data DWD is above the second threshold pulse state data ZD3 are determined, which show that the pulse state is Hua Mai. This is the second threshold set in advance so that it determines if the dicrotic wave property data DWD Ping may or Xuan may represent. In this example, the second threshold defined at 1.62.

A notification section 80 is of a type that outputs pulse state data ZD by display or voice. For example, the notification section shows 80 the characters "Hua mai", "Ping mai, Xuan mai" or symbols, eg pictograms, so that the person and a third party, eg a doctor, can recognize the pulse state.

1.3 Functioning of the Device for pulse wave examination

Next, the operation of the pulse wave inspection apparatus of the first embodiment will be described with reference to FIG 2 described.

Although a body movement component is superimposed on the MH signal due to the person's movement, that of the pulse state detection section 10 is output, first, the body movement component of the Körperbewegungskomponenteneliminierabschnitt 30 and the MHj signal showing only one pulse wave component becomes the FFT treatment section 40 passed (step S1 and step S2).

Subsequently, in the FFT treatment section 40 the MHj signal is subjected to FFT treatment to obtain the fundamental wave f1 of the pulse wave component and each of the harmonics f2 to f10 as pulse wave analysis data MKD, which are then supplied to the tidal wave characteristic extracting section 50 and the dicrotic wave extracting section 60 be routed (step S3).

After this step, the tidal wave property extracting section calculates 50 the ratio of the sum of the fifth harmonic f5, the sixth harmonic f6 and the seventh harmonic f7 to the fundamental wave f1 of the pulse waveform, which ratio expresses the characteristics of the tidal wave to obtain the tidal wave characteristic data TWD. The extracting section for the dicrotic wave property 60 calculates the sum of the second harmonic f2, the third harmonic f3 and the fourth harmonic f4 to the fundamental wave f1 of the pulse waveform, the ratio expressing the characteristics of the dicrotic wave to obtain the dicrotic wave characteristic data DWD (step S4).

Once the properties of the tidal wave and dicrotic wave of the pulse waveform are extracted in this way, the pulse state judgment section compares 70 First, the tidal wave characteristic data TWD having a first threshold value (step S5). When the tidal wave characteristic data TWD exceeds the first threshold (0.41), pulse state data ZD1 showing that the pulse state Xuan is mai is obtained in step S6.

On the other hand, if the tidal wave characteristic data TWD is below the first threshold value (0.41), the result of the judgment in step S5 is "no" and a judgment of the pulse state is made on the basis of the dicrotic wave characteristic data DWD in step S6. In this case, the pulse state judging section determines 70 whether the dicrotic wave characteristic data DWD is below a second threshold value (1.62) or not, and outputs pulse state data ZD2 in step S8 showing that the pulse state Ping may be when the dicrotic wave characteristic data DWD is below the second threshold value. On the other hand, when the dicrotic wave characteristic data DWD exceeds the second threshold (1.62), the result of the judgment in step S7 is "no", and pulse state data ZD3 showing that the pulse state Hua is mai is obtained in step S9.

On this manner is heeded in the first embodiment of the fact given that specialists who are trained in pulse diagnosis, the pulse state based on the tidal wave and the dicrotic wave judge the pulse waveform, and that the properties of the tidal Wave and the dicrotic wave at specific high harmonics appear, and the pulse waveform is subjected to a frequency analysis, about the properties of the tidal wave and the dicrotic wave too extract. Thus, the pulse state can be determined objectively and accurately become.

Second embodiment

Subsequently, will a device for pulse wave examination according to a second embodiment of the present invention.

In the foregoing first embodiment attention is paid to the fact that Hua Mai and Ping May be characterized by the dicrotic wave, Xuan may through the tidal wave is characterized, and the pulse waveform becomes subjected to an FFT treatment. Be based on the analysis each frequency components, the dicrotic wave and the tidal Correspond to wave, extracted to make a judgment based to take the extraction.

If now in the frequency analysis by FFT treatment no data on a a little longer Periods are present, no analysis result can be obtained. In general, therefore, FFT treatment will be applied to one pulse waveform over several Cycles executed.

The however, the dicrotic wave and the tidal wave appear in one sub-period in the pulse waveform. Therefore, if the frequency analysis only in the Periods executed which correspond to the dicrotic wave and the tidal wave, can further improve the judgment accuracy for the pulse state become.

consequently is in the second embodiment the pulse waveform using the wavelet transform, treated, taking a frequency analysis and time analysis simultaneously to specify the pulse state.

2.1 overall structure of Pulse wave device

Next, the structure of the pulse wave inspection apparatus according to the second embodiment is shown in FIG 3 shown. In the 3 The pulse wave examination apparatus shown is the same as the pulse wave examination apparatus shown in FIG 1 is shown, with the exception that a wavelet transform section 41 instead of the FFT treatment section 40 is used, a detection section for a tidal wave / dicrotic wave 42 , which specifies the time positions of the tidal wave and the dicrotic wave, and the internal structures of the tidal wave property extracting section 50 , the extracting section for the dicrotic wave property 60 and the pulse state evaluation section 70 differ from those used in the first embodiment. The second embodiment will be described below mainly with reference to the different points between the two embodiments.

2.2 wavelet transformation section

First, the structure of the wavelet transform section 41 described in detail with reference to the drawings.

wobei "b" der Parameter ist, der verwendet wird, wenn die Basisfunktion ψ(x) verschoben wird, während a der Parameter ist, wenn die Basisfunktion ψ(x) skaliert (erweitert) wird. In Gleichung (2) wird das Wavelet ψ((x – b)/a) gebildet, wenn die Basisfunktion ψ(x) nur um b verschoben wird und "a" mal erweitert wird. In diesem Fall wird die Breite der Basisfunktion ψ(x) entsprechend dem Skalenparameter a erweitert. 1/a entspricht daher der Frequenz. Der Wavelet-Transformationsabschnitt 41 ist so strukturiert, dass die Gleichung (2) berechnet wird. Die Einzelheit der Struktur ist wie in 4 dargestellt.Generally, in a time / frequency analysis that captures signals in both time and frequency, a wavelet is a unit that cuts out a portion of the signal. The wavelet transform specifies the size of each part of the signal that is cut out by this unit. As a basic function for defining the wavelet transform, a function ψ (x) located in both time and frequency is introduced as a base function (mother wavelet). Here the wavelet transformation is defined by the basis function ψ (x) of a function f (x) as follows.

where "b" is the parameter used when the base function ψ (x) is shifted, while a is the parameter when the base function ψ (x) is scaled (expanded). In Equation (2), the wavelet ψ ((x-b) / a) is formed when the basis function ψ (x) is shifted only by b and "a" times expanded. In this case, the width of the basis function ψ (x) is extended according to the scale parameter a. 1 / a therefore corresponds to the frequency. The wavelet transform section 41 is structured so that the equation (2) is calculated. The detail of the structure is as in 4 shown.

In 4 becomes a MHj signal generated by a body movement component eliminating section 30 is output to a waveform shaping section 400 and an A / D converter 410 directed. The Wel lenformformungsabschnitt 400 determines a control signal C and a clock CK which are synchronized with the pulse waveform MHk.

Here is a block diagram of the waveform shaping section 400 in 5 shown. In 5 is a ringing filter 401 a filter with a high Q value, where the center frequency is 2.2 Hz and the passband is 0.8 Hz to 3.5 Hz. Since the fundamental wave component of the pulse waveform is generally in the range of 0.8 Hz to 3.5 Hz, the fundamental wave component is extracted when the pulse waveform MHj is passed through the ringing filter 401 goes. If, for example, in 6 is shown, the pulse waveform MHj in the ringing filter 401 is input, the output is the one in 6 when " 401 out "is shown.

Subsequently, a zero-crossing detection circuit comprises 402 a comparator and the like and compares an output signal from the ringing filter 401 with the base level to get a rectangular wave. The rectangular wave is synchronized with the pulsation. If, for example, the signal from the ringing filter 401 that's what's called " 401 out "in 6 is the output signal from the zero-crossing detection circuit 402 that as " 402 out "is shown in the same figure.

Then form a comparison section 403 , a loop filter 404 , a voltage control oscillation circuit 405 and a frequency divider 406 a phase locked loop. When an output signal from the zero-crossing detection circuit 402 and an output signal from the frequency divider 406 to the one input terminal and the other input terminal of the comparison portion, respectively 403 are passed, gives the comparison section 403 an error signal corresponding to a phase difference between the two output signals. When the error signal to the voltage control oscillation circuit 405 over the loop filter 404 is passed, gives the voltage control oscillation circuit 405 a clock signal CK. The clock signal CK is from the frequency divider 406 divided into 1 / N, and to the other input terminal of the comparison section 403 returned. For example, when the division ratio is 1/8, the frequency of the clock signal CK becomes 8 times the frequency of the output signal from the zero-crossing detection circuit 402 how with " 405 out CK "in 6 shown. The clock signal CK is then in a frequency divider 407 divided in half and as control signal CS, as in 6 shown, issued.

The pulse waveform MHj is also from an A / D converter 410 who in 4 is converted into a digital signal, and the digital signal is then stored in a first memory 420 and a second memory 430 saved. Here, the control signal CS becomes directly a write terminal of the first memory 420 directed. The control signal CS is from an inverter 440 and the reverse signal becomes a write terminal of the second memory 430 directed. Thus, the first and second memories store 420 . 430 the pulse waveform MH alternately at intervals of the period.

The symbol 450 FIG. 12 illustrates a multiplexer that selects the pulse wave data MD alternately from the first and second memories 420 . 430 to output the selected data to a basic function development section W. In this way, the pulse wave data MD becomes during the writing time of the first memory 420 from the second memory 430 read out, and the pulse wave data MD are in the second memory during the reading time of the first memory 420 written.

Further The basic function development section W has a structure that allows the calculation of the previous equation (2). The above-mentioned clock signal CK becomes the basic function development section W is directed and a calculation process is at intervals of the period executed. The basic function development section W includes a basic function storage section W1 for storing the basic function ψ (x), a scale conversion section W2 for converting the scale parameter a, a buffer memory W3, a translation section W4 for performing a parallel shift, and a multiplication section W5. It is stated that if the basis function ψ (x) is stored in the basic function storage section W1, a Gabor wavelet, a Mexican hat wavelet, a Harr wavelet, a Meyer wavelet, a Shannon wavelet and the like, and in this embodiment a base function called symlets 5 is used, to advantageously extract the characteristics of the pulse waveform.

When the basic function ψ (x) is read from the basic function storage section W1, the scale conversion section W2 executes the conversion of the scale parameter "a". Here, the scale parameter "a" corresponds to the period. Therefore, if "a" is increased, the basis function ψ (x) is extended on the time axis. In this case, since the data volume of the basic function ψ (x) stored in the basic function storage section W1 is fixed, the data volume is reduced as "a" is increased. The scale conversion section W2 executes a compensation treatment for compensating the data reduction and performs a lowering treatment when "a" is small to obtain a function ψ (x / a). This data is once stored in the buffer memory W3.

Then reads the translation section W4 the function ψ (x / a) from the buffer memory W3 with a timing that the translation parameter b corresponds to the function ψ (x / a) to shift, whereby a function ψ ((x-b) / a)) is obtained.

Then, a multiplying section W5 multiplies a variable 1 / a ^1/2 by the function ψ ((x-b) / a)) and the pulse wave data MD to perform a Wafelet transformation every beat, so that the pulse wave analysis data MKD is obtained , In this embodiment, the pulse wave analysis data MKD is divided into frequency ranges, for example, 0 Hz to 0.5 Hz, 0.5 Hz to 1.0 Hz, 1.0 Hz-1.5 Hz, 1.5 Hz to 2.0 Hz , 2.0 Hz-2.5 Hz, 2.5 Hz to 3.0 Hz, 3.0 Hz-3.5 Hz, and 3.5 Hz to 4.0 Hz, and output.

2.3 detection section for the tidal wave / dicrotic wave

Subsequently, a tidal wave / dicrotic wave detection section compares 42 the pulse wave analysis data MKD in a certain frequency range with a threshold value to obtain control signals ct and cd specifying the time positions of the tidal wave and the dicrotic wave, respectively.

For example, in the pulse waveform MHj, those in 7 , the tidal wave and the dicrotic wave are represented by tw and dw, respectively. When the wavelet transform of this pulse waveform MHj is performed, the result of the wavelet analysis as shown in the same figure is obtained. In the result of the analysis, the values of the pulse wave analysis data MKD are represented by shadings. The darker the color of the parts, the larger the values of the pulse wave analysis data MKD, while the brighter the color of the parts, the smaller the pulse wave analysis data MKD.

Out the figure can be seen that the areas A and B, that of the parts (White) with a small value for the pulse wave analysis data MKD are surrounded, arranged in a time domain which corresponds to the tidal wave. The part with a small one Value in the sense of the pulse wave analysis data in the direction of the Y or Frequency axis shows that the energy of the pulse waveform MHj in their period is at a low level. In this part is the Pulse waveform MHj flat. For example, the boundary between the areas A and B of a tip of the tidal wave tw.

When considering a certain frequency range, the time position of the tidal wave tw can be detected due to its change. In this embodiment, comparing the value of the pulse wave analysis data MKD in a threshold frequency range X with a control signal ct specifying the time positions between t1 and t2 of the tidal wave tw, as in FIG 7 is shown. On the other hand, comparing the value of the pulse wave analysis data MKD in a threshold frequency range Y with a control signal dw specifying the time positions between t3 and t4 of the tidal wave tw, as in FIG 7 is shown.

2.4. Extracting section for the tidal wave feature and extract section for the dicrotic wave property

First, the extracting section specifies the tidal wave property 50 the time position of the tidal wave on the basis of the control signal ct and adds data in a specific frequency range from the pulse wave analysis data MKD in the specified period.

The wavelet transform section 41 For example, it is constructed to be formed of a filter bank in which the characteristics of a high-frequency filter 1A and a low frequency filter 1B are changed by the clock signal CK synchronized with the pulse waveform MHj as described later in the section "14 Other Embodiments" (6) with reference to FIG 58 is mentioned. In this case, when the pulse wave analysis data corresponding to the fundamental wave f1 of the pulse waveform MHj is M * 1, the parts showing the properties of the tidal wave appear on the fifth harmonic f5 to the seventh harmonic f7, and thus the wavelet transforming section adds 41 M * 5, M * 6 and M * 7 for calculating the tidal wave property extraction data TWD.

Subsequently, the extracting section specifies the dicrotic wave property 60 the time position of the dicrotic wave on the basis of the control signal cd, and adds data in a specific frequency range from the pulse wave analysis data MKD in this period.

If the wavelet transform section 41 is formed with a construction, for example, for the tidal wave characteristic extracting section 50 and the pulse wave analysis data corresponding to the fundamental wave f1 of the pulse waveform MHj are M * 1, the parts showing the characteristics of the dicrotic wave appear on the second harmonic f2 to the fourth harmonic f4, and thus the wavelet transforming section 41 M * 2, M * 3 and M * 4 for calculating the dicrotic wave property extraction data DWD.

In this way, the extracting section for the tidal wave property is extracted 50 and the dicrotic wave extracting section 60 the properties of the tidal wave and the dicrotic wave in terms of the time domain as well as the frequency domain, by making clever use of the property of the wavelet transform that can divide the waveform into a frequency domain and a time domain to perform waveform analysis. The properties can thus be extracted with high accuracy.

2.5 pulse state judgment section and notification section

Subsequently, a pulse state judgment section compares 70 the tidal wave property extraction data TWD and the dicrotic wave property extraction data DWD with each threshold value to judge the pulse state, such as Ping may, Hua mai or Xuan may to determine pulse state data ZD. A notification section 80 indicates the person or a third party, eg, a doctor, the pulse state data ZD on a display by a voice or the like in the same manner as in the first embodiment.

According to the device to the pulse wave examination of the second embodiment, as before mentioned, the frequency component is analyzed in a limited period, in which the tidal wave and the dicrotic wave appear by a wavelet transformation of the pulse waveform is performed, which is captured by the person. As a result, the properties of the tidal wave and the dicrotic wave are extracted exactly to thereby making an accurate assessment of the pulse state.

Third embodiment

3.1 Principle of the third embodiment

The Pulse waveform presses the pulsation off when the bloodstream passing through the contraction of the heart is pumped out to an aorta, through an artery flows, and thus has a certain period that synchronizes with the heartbeat is. On analysis techniques for analyzing a periodic waveform, to determine their properties include a spectrum analysis, which is represented by FFT (Fast Fourier Transformation). The inventors However, the present invention found an autocorrelation function, which can be handled with a simple calculation.

When an irregular variation is represented by x (t) and x (t) has a periodic variation in a period T, x (t) is given by the following equation: x (t) = x (t ± nT) where n = 0, 1, 2, ...

A Waveform represented by the above equation overlaps the original waveform, if a whole multiple of the period is moved. When the irregular variation x (t) is strongly periodic is, the waveform becomes similar the original waveform, if on the time axis through a whole Multiple of the period is moved. The similarity of a waveform, which moved by a certain time τ is, with the original waveform is examined, and the correlation between x (t) and x (t + τ) becomes as required calculated to be a periodic component in the variations too differ.

When the irregular variation as a function of time is expressed by x (t), the autocorrelation function is defined as the average value of the product of two variations separated by an interval τ (time) and given by the following equation: C (τ) = E [x (t) x (t + τ)] where E is an average, but can be replaced by the time average in a steady state stochastic process. Thus, the autocorrelation function C (τ) can be expressed as follows:

Also, a value obtained by dividing the autocorrelation function C (τ) by the value calculated when τ = 0 is expressed as an autocorrelation function coefficient R (τ) given by the following equation: R (τ) = C (τ) / C (0) = E [x (t) x (t + τ) / E [x 2 (T)]

16 to 18 show the autocorrelation function coefficients of a Xuan may, as in 45C pictured, a ping mai, as in 45A represented, or a Hua Mai, as in 45B shown. Comparing these figures, a ripple in the waveform of the autocorrelation coefficient R (τ) becomes noticeable when the pulse state changes from Xuan may to Hua mai via Ping mai. This is consistent with the fact that Hua may has a smooth waveform, Ping may contain three peaks, but these peaks are small in size, and Hua may contain two large peaks. In other words, the characteristics of each waveform are reflected in the autocorrelation coefficient R (τ). The waveform of the autocorrelation coefficient R (τ) is further obtained on the basis of a pulse waveform formed over a relatively long period, and thus the characteristics of the pulse waveform can be determined with accuracy.

The instantaneous size of the autocorrelation coefficient R (τ) is, other than the instantaneous size of the pulse waveform, given as a time average. Even if therefore the SN ratio of the Pulse waveform detected in a living body is somewhat impaired the average of the noise is determined, with the result that's the SN ratio is improved. Further, the autocorrelation coefficient R (τ) is normalized the autocorrelation function C (τ) is formed, and is thus for analysis by comparing pulse waveforms with different amplitudes practical.

Out For the above reason, the inventors of the present invention determined Invention a criterion that specifies the pulse state by the property of the autocorrelation coefficient R (τ) is used wisely will, and have found a device for pulse wave examination, the pulse state of the living body based on the criterion reviewed.

3.2 Electrical structure the device for pulse wave examination

Next, the electrical structure of the pulse wave inspection apparatus will be described with reference to FIG 19 described. 19 Fig. 10 is a block diagram showing the electrical structure of the pulse wave inspection apparatus.

The device for pulse wave examination 1 includes the pulse wave detection section 10 for detecting the pulse waveform MH, an autocorrelation calculation section 210 for calculating autocorrelation data RD on the basis of the pulse waveform MH, a pulse state data acquisition section 220 for obtaining the pulse state data ZD on the basis of the autocorrelation RD, and a display section 230 ,

First, the autocorrelation calculation section includes 210 a waveform treatment section 211 , a store 212 , a multiplication section 213 , an average value calculating section 214 and a normalization calculation section 215 , The memory 212 stores the pulse waveform MH in a period of at least one beat. Incidentally, if the autocorrelation function C (τ) is to be calculated according to Equation (3), x (t) x (t + τ) must be integrated from -T72 to T72 (T is infinite). However, in view of the fact that x (t) in this embodiment is the pulse waveform MH synchronized with the beat period, the calculation based on the pulse waveform MH can be made in a period of at least one beat. In this embodiment, therefore, the waveform shaping of the pulse waveform MH by the waveform treatment section becomes 211 is executed, the shaped waveform is converted into a rectangular wave synchronized with the pulse wave period, and a write control signal WE for controlling the writing operation of the memory 212 is obtained on the basis of the rectangular wave. For example, the pulse waveform MH in four periods by the write control signal WE in the memory 212 written.

Subsequently, the multiplication section reads 213 a pulse waveform MH1 corresponding to x (t), and a pulse waveform MH2 corresponding to x (t + τ) multiplies the two, and outputs the result of the multiplication. The average value calculation section 214 calculates the average of MH1 · MH2 according to the average of x (t) x (t + τ), and outputs the result of the calculation.

Subsequently, the normalization calculation section normalizes 215 the result, that of the average value calculation section 214 was calculated by the autocorrelation function C (0) to obtain the autocorrelation data RD. In particular, the normalization is performed with the average of X ² (t), namely MH ^{1 2} . As a result, the autocorrelation data RD shows the autocorrelation coefficient R (τ) of the pulse waveform MH.

Here, the autocorrelation coefficient RD for the pulse waveform MH of each pulse state checked in 45A to 45C is shown. As in 16 First, the minimum value of the autocorrelation coefficient R (τ) is 0.2 at Xuan may. As in 17 and 18 On the other hand, the minimum value of the autocorrelation coefficient R (τ) is 0.32 and 0.3 at Ping may and Hua mai, respectively. The pulse state is therefore judged as Xuan may if the minimum value of the autocorrelation coefficient is less than 0.25.

Thereafter, the ratio of a period in which the autocorrelation R (τ) is greater than 0.5 to a period of a beat is 60% or higher at Ping may (see 17 ) and 34% at Hua mai (see 18 ). Therefore, the pulse state may be judged as Ping may if this ratio exceeds 47% and Hua may if the ratio is less than 47%.

The pulse state data acquisition section 220 judges the pulse state based on the above evaluation criteria. The pulse state data acquisition section 220 includes a minimum value detection section 221 and a first comparison section 222 for detecting a pulse state of Xuan may, a time measuring section 223 , a calculation section 224 and a second comparison section 225 for detecting a pulse state of Ping mai or Hua mai, and a data acquisition section 226 for obtaining the pulse state data ZD.

First, the minimum value detection section detects 221 the minimum value of the autocorrelation data RD in a period corresponding to one period of one beat. The first comparison section 222 determines whether or not the detected minimum value is less than 0.25, and outputs the result of the judgment to the data acquisition section 226 out.

Then the time measurement section compares 223 the autocorrelation data RD having a prescribed threshold value (0.5) and measures a time interval in which the autocorrelation data RD exceeds the threshold value (0.5). The calculation section 224 calculates the ratio of the measured time interval to a period of a beat. Incidentally, the period of a beat is determined from the above waveform treatment section 211 to be forwarded. The second comparison section 225 determines if the calculated result exceeds a prescribed threshold (47%).

Subsequently, the data acquisition section determines 226 the pulse state data ZD on the basis of each result included in the first and second comparison sections 222 and 225 is determined. If first the minimum value in the first comparison section 222 is judged to be less than 0.25, the pulse state data ZD1 indicating Xuan may be determined. When the period in which the autocorrelation data RD exceeds 0.5, in the second comparison section 225 is judged to be more than 47%, the pulse state data ZD2 indicating Ping may be obtained, while if the period is judged to be less than 47%, the pulse state data ZD3 indicating Hua mai may be obtained.

Subsequently, the display section comprises 230 a ROM, a control circuit, a liquid crystal display device, and the like. When the pulse state data ZD to the display section 230 This detects the control circuit, reads the characters stored in the ROM, and displays these characters on the liquid crystal display. As symbols, specific symbols or pictograms, as well as the characters "Ping mai", "Xuan mai" and "Hua mai" can be used. The display section 230 Allows the user or a doctor to be notified of the physical condition.

The function of the device for pulse wave examination 1 can be described this way. In the apparatus used in practice, the autocorrelation calculation section is composed 210 and the pulse state data acquisition section 220 from CPUs, memories and the like. In this case, the CPU goes through various calculation processes and comparison processes based on the control programs stored in a part of the memories to obtain the pulse state data ZD.

3.3 Functioning of the Device for pulse wave examination

Next, the operation of the pulse wave inspection apparatus according to the third embodiment of the present invention will be described with reference to the drawings. 20 FIG. 4 is a flowchart showing the operation of the pulse wave examination apparatus. FIG.

First, the pulse wave detection section detects 10 the pulse waveform MH (step S1).

When the pulse waveform MH to the autocorrelation calculation section 210 is passed, the pulse waveform MH is in the memory 212 written and later read out in a fixed period. An autocorrelation function is calculated on the basis of the read pulse waveform MH, and the calculated result is normalized to obtain the autocorrelation data RD indicative of the autocorrelation coefficient R (τ) (step S2).

Thereafter, the pulse state obtaining section acquires 220 the pulse state data ZD on the basis of the autocorrelation data RD in the following manner. When the minimum value of the autocorrelation data RD corresponding to one period of a heartbeat in the minimum value detection section 221 is detected (step S3), first determines the first comparison section 222 Whether the minimum value is less than 0.25 or not (step S4). If the minimum value is less than 0.25, the result of the determination is given as YES, and the step goes to the next step (step S5), in which the pulse state is judged to be Huan may to the pulse state data ZD1 in the data acquisition section 226 to win.

On the other hand, if the minimum value is 0.25 or more, the result of the determination is given as NO, and a judgment is made as to whether the pulse state is Ping may or Hua mai. In this case, the time measurement section measures 223 a time interval in which the autocorrelation data RD exceeds 0.5 in a period corresponding to a period of one heartbeat (step S6), and the calculating section 224 calculates the ratio of the measured time to the period of a beat.

Then the second comparison section determines 225 whether the result is that in the calculation section 224 was calculated to exceed 47% or not (step S8). If this result exceeds 47%, the step proceeds to the next step (step S9), in which the pulse state is judged as Pingmai, so that the data acquisition section 226 the pulse state data ZD2 can win. On the other hand, if the result in the calculation section 224 is calculated 47% does not exceed the step proceeds to the next step (step S10), in which the pulse state is judged as Hua mai to the pulse state data ZD3 in the data acquisition section 226 to win.

As mentioned above, the device judges the pulse wave examination 1 According to the third embodiment, the pulse state based on the autocorrelation data RD of the pulse waveform MH, and thus the person or the doctor can know the current state from the detected result of the pulse wave.

3.4 Modification of the third embodiment

• (1) In the foregoing third embodiment, the minimum value detection section calculates 221 the autocorrelation data RD in one period of a heartbeat. The minimum value detection section 221 however, may be arranged so that the average of the minimum values of the autocorrelation data RD acquired in each of the several heartbeat periods is calculated to determine the average of the minimum values. In this case, since the average of the minimum values is calculated, variations in the minimum values caused by noise can be restrained. This can improve the accuracy in determining whether the pulse state is Hua mai or not.
• (2) Although in the above-mentioned third embodiment, the calculating section 224 calculates the ratio of the measured time to the period of a heartbeat, the average of the ratios detected in each of the multiple heartbeat periods to output the average ratio can be calculated. This can improve the accuracy in determining whether the pulse state is Ping may or Hua mai, since the average of the ratios is calculated to thereby limit variations caused by noise.
• (3) Comparing the autocorrelation coefficients R (τ) of a typical Ping may and Hua mai (see 17 and 18 ), a difference in width between the autocorrelation coefficients R (τ) in the range of 0.4 to 0.8 can be observed. Therefore, the time measuring section 223 measure a time interval, in which the autocorrelation coefficient exceeds a prescribed threshold value ranging between 0.4 and 0.8, and the second comparison section 225 may determine whether the pulse state is Ping may or Hua mai based on the time interval corresponding to this threshold.

Fourth embodiment

Subsequently, will a device for pulse wave examination of a fourth embodiment of the present invention.

4.1 Electrical structure the device for pulse wave examination

The electrical structure of the pulse wave inspection apparatus of the fourth embodiment is the same as that of the third embodiment except for the structure of a pulse state data acquisition section 220 ,

The electrical structure of the pulse state data acquisition section 220 according to the fourth embodiment will be described as follows. 21 Fig. 10 is a block diagram of the pulse state data acquisition section 220 according to the fourth embodiment.

The pulse state data acquisition section 220 in this embodiment comprises a minimum value detection section 221 and a first comparison section 222 for determining whether the pulse state is Hua mai or not, a change rate calculating section 227 , a maximum value detection section 228 and a second comparison section 225 for determining whether the pulse state is Ping may or Hua may, and a data acquisition section 226 for obtaining pulse state data ZD on the basis of these determined results.

First, the first comparison section determines 222 Whether the pulse state is Xuan may or not, depending on whether the minimum value of the auto-correlation data RD, that of the minimum value detection section 221 was detected, exceeds 0.25 or not, as in the third embodiment.

Subsequently, the change rate calculation section calculates 227 the rate of change RDd of the autocorrelation data RD. If the autocorrelation data RD is as in 16 to 18 Any change rate RDd of Xuan Mai, Ping Mai and Hua Mai is as in 22 shown. As can be seen from this figure, the maximum value of the rate of change RDd is about 0.1 at Hua mai, while it is 0.072 at Ping mai. This corresponds to the fact that the ripple of the pulse waveform MH of Ping may be larger than that of the pulse waveform of Hua mai. Therefore, it can be determined by the maximum value of the rate of change RDd, whether the pulse state is Ping may or Hua mai. When the maximum value of the rate of change RDd exceeds 0.085, the pulse state may be determined as Hua mai, while if it does not exceed 0.085, the pulse state may be judged accordingly as Ping mai.

Then, the maximum value detection section detects 228 the maximum of the rate of change RDd in a prescribed time period that is longer than one period of a beat. The second comparison section 225 compares the maximum value of the rate of change with a prescribed threshold (0.85) for determining whether or not the maximum rate of change rate RDd exceeds the threshold.

The data collection section 226 obtains pulse state data ZD on the basis of each result obtained from the first and second comparison sections 222 and 225 is determined. If the minimum value in the first comparison section 222 is judged to be less than 0.25, a pulse state ZD1 indicating Hua mai is obtained. If then the maximum value of the rate of change RDd in the second comparison section 225 is judged to be less than 0.85, pulse state data ZD2 indicating ping may be obtained, while when judged to exceed 0.85, pulse state data ZD3 indicating Hua may be obtained.

4.2 Functioning of the Device for pulse wave examination

Next, the operation of the pulse wave inspection apparatus of the fourth embodiment will be described. 23 FIG. 4 is a flowchart showing the operation of the pulse wave examination apparatus. FIG. The operations from step S1 to step S5 are the same as those of the pulse wave inspection apparatus of the third embodiment described with reference to FIG 20 has been described, and therefore a description of these steps will be omitted.

When in step S11, the change rate calculating section 227 detects the rate of change RDd of the autocorrelation data RD, the maximum value detection section detects 228 the maximum value of the rate of change RD in a period corresponding to one period of a strike (step S12). For example, if the calculated rate of change RDd is that of Hua mai, as in 22 is shown, a value of about 0.1 is detected as the maximum value.

Then the second comparison section determines 225 whether the maximum value exceeds 0.85 or not. If the maximum value proves to be less than 0.85, the step proceeds to step S14, where the pulse state is judged as Pingmai, and the data acquisition section 226 gains pulse state data ZD2. On the other hand, if it shows that the maximum value exceeds 0.85, the step proceeds to step S15, where the pulse state is judged to be Hua mai, and the data acquisition section 226 generates pulse state data ZD3.

In the fourth embodiment will, as previously mentioned, paid attention to the point that a difference between ping May and Hua may in the maximum value of the rate of change RDd of the autocorrelation data RD is present. The maximum value of the rate of change RDd is determined by the Threshold compared to determine whether the pulse state Ping May or Hua Mai. Thus, even a person who has no knowledge in the pulse detection has to detect the exact pulse state.

Fifth embodiment

In the device for pulse wave examination 1 According to the third and fourth embodiments, the autocorrelation data RD are obtained on the basis of the pulse waveform MH received from the pulse wave detection section 10 be issued to assess the pulse state. However, when a person walks and lives everyday life, body movement causes a fluctuation in the person's bloodstream. Therefore, a component due to the body movement is superimposed on the pulse waveform MH received from the pulse wave detection section 10 is issued. The size of the body movement component depends on the degree of movement. When the amount of movement is large, the body movement component superimposed on the pulse waveform MH increases, making it difficult to make an accurate judgment of the pulse state. Thus, in the fifth embodiment of the present invention, the body movement component is eliminated from the pulse waveform MH, and the pulse state is judged on the basis of the obtained pulse waveform.

5.1 Electrical structure the device for pulse wave examination

24 Fig. 10 is a block diagram showing the electrical structure of the pulse wave inspection apparatus according to the fifth embodiment of the present invention. Each structure of the autocorrelation calculation section 210 , the pulse state data acquisition section 220 and the display section 230 in this embodiment is the same as that described in the third and fourth embodiments, and therefore further description of these portions will be omitted. Likewise, a body movement eliminating section 30 and sections before this section, namely a pulse wave detection section 10 , a body movement detection section 20 , a review section 22 and a waveform treatment section 21 , the same as those described in the first embodiment. Therefore, a further description of these sections is omitted.

The pulse wave examination apparatus of this embodiment provides a body movement-eliminated pulse waveform MHj due to the above-mentioned structure. The autocorrelation calculation section 210 may obtain the autocorrelation data RD on the basis of the body movement-eliminated pulse waveform MHj. According to the device for pulse wave examination 1 In this embodiment, the pulse state can be specified in a state free from the influence of the body movement.

Sixth embodiment

Subsequently, a device for pulse wave examination 1 according to a sixth embodiment of the present invention.

25 is a block diagram of a pulse wave examination apparatus 1 according to the sixth embodiment. Although in the sixth embodiment, a body movement component TH using a body movement detection section 20 and a waveform treatment section 21 is detected as in the fifth embodiment, the sixth embodiment is different from the fifth embodiment Embodiment in that the elimination of body movement, which is mentioned in the fifth embodiment, using a wavelet transform.

6.1 First and second Wavelet transform section and first and second correction sections

In 25 performs a first wavelet transform section 243 a well-known wavelet transformation of a pulse waveform MH from the pulse wave detection section 10 is output to obtain pulse wave analysis data MKD. Then the second wavelet transform section leads 245 a well-known wavelet transformation of a body motion waveform TH from the body motion detection section 20 is output to obtain body movement analysis data TKD. This first and second wavelet transform section 243 and 245 have the same structure as those described in the second embodiment.

26 shows the pulse wave analysis data MKD in a part of the period of the pulse waveform MH. In the figure, a period T is near a peak P4, and the pulse wave analysis data MKD are obtained at time intervals set by dividing the period T into 8 parts. On the other hand, in the wavelet transformation, the frequency resolution and the time resolution are in a mutually dependent relationship. Therefore, if the frequency resolution is sacrificed, the pulse wave analysis data can be obtained at smaller intervals.

The first frequency correction section 244 Performs frequency corrections of the pulse wave analysis data MKD. In the above equation (2), there is the term "1 / a ^1/2 " which corresponds to the frequency. The effect of this term must be corrected when comparing data between different frequency zones. A first frequency correction section 244 is therefore provided and multiplies wavelet data WD by a factor a ^1/2 to obtain pulse wave corrected data MKDa. This allows a correction on the basis of each corresponding frequency, so that a constant energy density per frequency is obtained. Furthermore, the second frequency correction section leads 246 the frequency correction of the body movement analysis data TKD in the same manner as in the case of the first frequency correction section 244 to generate body movement corrected data TKDa from the body movement analysis data TKD.

6.2 Body Movement Component Elimination Section

Subsequently, a body movement component eliminating section subtracts 240 the body movement corrected data TKDa from the pulse wave corrected data MKDa to obtain body movement-eliminated pulse wave data MKDaj. This is described in detail. Incidentally, in the following description, the body movement is analyzed on the assumption that the person lifts a cup with his hand and then returns it to the original position. In this case, the pulse waveform MH which is in 27 is shown by the pulse wave detection section 10 and at the same time, the body waveform TH becomes the body movement detection section 20 detected.

Here, the body waveform TH starts rising from time T1, reaches a positive peak at time T2, gradually decreases, goes through a level 0 at time T3, reaches a negative peak at time T4, and returns to a level 0 at time T5. The body movement waveform TH is obtained from the body movement detection section 20 detected using an acceleration sensor. The time T3 corresponds to the time when the person raised the cup to the maximum height, the time T1 corresponds to the time when the lifting starts, and the time T4 corresponds to the time when the lifting is finished. Therefore, the period between the time T1 and the time T4 is the period in which the body movement exists. The pulse waveform MHj, which in 27 is a pulse waveform that is formed on the assumption that there is no body movement. Also in this embodiment, the frequency of the fundamental wave of the pulse waveform MH is 1.3 Hz.

28 shows the pulse wave corrected data MKDa in a period Tc (see 27 ) and 29 shows the body movement corrected data TKDa in the period Tc. From this figure, it can be seen that the frequency components having a relatively large level are present in a frequency zone between 0.0 Hz and 1.0 Hz in the body movement waveform TH. When the pulse wave corrected data MKDa and the body movement corrected data TKDa are related to the body movement eliminating section 240 The body movement eliminating section subtracts 240 the body movement corrected data TKDa from the pulse wave corrected data MKDa to gain body movement-eliminated pulse wave data MKDaj which excludes the body movement component, as in 30 is shown.

This allows an elimination of the effect of body movement, even if the body movement is available.

6.3 Assessment Section

Subsequently, the judging section compares 22 the body movement waveform TH having a prescribed threshold value to obtain a control signal C indicative of the presence or absence of body movement, and supplies this signal to the waveform treatment section 21 , the second wavelet conversion section 245 and the second frequency correction section 246 , This guarantees that every operation of the wavelet treatment section 21 , the second wavelet conversion section 245 and the second frequency correction section 246 is interrupted when there is no body movement, thereby reducing the computation time and energy consumption, and improving the SN ratio.

6.4 Inverse Wavelet Transformation Section

Subsequently, an inverse wavelet transform section leads 247 the inverse wavelet transformation of the body motion-eliminated pulse wave data MKDaj to obtain a body motion-eliminated pulse waveform MHj. In this case, the inverse wavelet transform section leads 247 the inverse wavelet transform based on equation (4) to reconstruct the waveform.

Then, the autocorrelation calculation section generates 210 as in the fifth embodiment, autocorrelation data RD based on the body motion-eliminated pulse waveform MHj.

Thereafter, the pulse state data acquisition section acquires 220 Pulse state data ZD on the basis of the autocorrelation RD and the display section 230 then indicates such characters as "Ping mai", "Xuan mai" and "Hua mai" indicated by the pulse state data ZD or characters corresponding to each pulse state. The display section 230 guarantees that the person or the doctor can determine the pulse state.

As previously stated, is the sixth embodiment designed so that the autocorrelation data RD on the basis of Body movement-eliminated Pulse waveform MHj be obtained, excluding a body movement component is, and the person thus their pulse state continuously in the everyday life can capture.

Seventh embodiment

In the fifth and sixth embodiments, the body movement waveform TH becomes the body movement detection section 20 is detected, the pulse waveform MH is compared with the body motion waveform TH, a body motion component included in the frequency component of the pulse waveform MH is eliminated to calculate the autocorrelation data RD, thereby specifying the pulse state. However, the above structure needs the body movement section 20 and the waveform treatment section 21 , which complicates the structure. A seventh embodiment of the present invention is developed in view of this situation, and provides a pulse wave examination apparatus which has a simple structure and can accurately detect a pulse state even when there is a body movement.

31 FIG. 12 is a block diagram of the pulse wave examination apparatus according to the seventh embodiment, which is the same as the pulse wave examination according to the sixth embodiment shown in FIG 25 is shown with the exception that the body movement detection section 20 , the waveform treatment section 21 , the second wavelet transform section 245 and the second frequency correction section 246 are absent, and with the exception of the internal structure of the body movement eliminating section 240 , The following is a description of the difference between the two embodiments.

A body movement eliminating section 240 separates and removes a body movement component from the pulse wave corrected data MKDa to obtain body movement-eliminated pulse wave data MKDaj. Here the body movement eliminating section uses 240 the property of body movements as mentioned below.

The body movement gets through the up and down movement of an arm or the swinging of an arm. There are, however few possibilities to experience a momentary movement of the living body in everyday life. The frequency component of the body motion waveform TH is not very high and is usually found in everyday life a range between 0 Hz and 1 Hz. In this case, the majority of the Frequency of the fundamental wave of the pulse waveform in a range between 1 Hz and 2 Hz. In everyday life, therefore, is the frequency component the body movement waveform TH in a frequency zone lower than the fundamental frequency of Pulse waveform MH is.

on the other hand is in the operation of sports, e.g. while jogging, the frequency component the body movement waveform TH easily by the action of pivotal movement of an arm and the like elevated. The Number of punches but takes in proportion to the extent of Movement to, and the frequency of the fundamental wave of the pulse waveform MH is thereby increased simultaneously. Therefore, even while of a sport, the frequency component of the body movement waveform TH in a frequency zone, which is generally lower than the fundamental frequency the pulse waveform is MH.

The body movement eliminating section 240 separates a body movement component taking into account the above fact. In particular, it is structured such that a frequency zone lower than that of the fundamental wave component of the pulse waveform MH is neglected. In this case, if the body movement component is present in a frequency zone higher than that of the fundamental wave component of the pulse waveform MH, the accuracy in the detection of the cardiac function is reduced. However, as mentioned above, the probability that the body movement component is in a frequency zone lower than that of the fundamental wave component of the pulse waveform MH is high. The pulse state can therefore be diagnosed with high accuracy.

32 Fig. 10 is a block diagram of the body movement eliminating section 240 , A waveform shaping section 310 provides the pulse waveform MH with waveform shaping and obtains a reset pulse synchronized with the pulse waveform MH. A counter 302 measures the number of clock pulses, though not shown. The count of the counter 302 is reset by the above reset pulse. An average value calculation circuit 303 calculates the average value of the count of the counter 302 , In this case, the average value represented by the average value calculation circuit corresponds 303 is calculated, the mean period of the pulse waveform MH. The frequency of the fundamental wave of the pulse waveform MH can be detected by referring to the average value.

Subsequently, a substitution circuit specifies 304 a frequency range including the frequency of the fundamental wave of the pulse waveform MH based on the above-mentioned average value. For example, when the average value shows 0.71 seconds, the frequency of the fundamental wave becomes 1.4 Hz. The frequency range to be specified becomes 1 Hz to 1.5 Hz. Then, the substitution circuit replaces 304 the pulse wave corrected data MKDa by 0 in a frequency range lower than a specified frequency range to obtain the body motion-eliminated pulse wave data MKDaj. A component of a frequency range which is lower than the frequency of the fundamental wave of the pulse waveform MH is thereby neglected. In this case, a pulse wave component as well as a body movement component are replaced by 0. However, since the characteristic portion of the pulse waveform MH is present in a frequency zone higher than the frequency of the fundamental wave of the pulse waveform MH, replacing the pulse wave component with 0 has almost no effect on the pulse waveform.

For example, if the pulse waveform MH (the frequency of its fundamental: 1.3 Hz), which is in 27 is shown by the pulse wave detection section 10 is detected, the pulse wave corrected data MKDa in the period Tc, as in 28 shown.

In this case, the frequency zone is that of the substitution circuit 304 is specified in a range between 1.0 Hz and 1.5 Hz, and thus the frequency zone undergoing substitution ranges between 0.5 Hz and 1.0 Hz and between 0 Hz and 0.5 Hz Data in a frequency range between 0 and 1 Hz in the pulse wave-corrected data MKDa is replaced by 0 and the body motion-eliminated pulse wave data MKDaj included in 33 are shown are obtained.

When the body movement-eliminated pulse wave data MKDaj obtained in this way is added to the body motion-eliminated waveform MHj by the inverse wavelet transform section 248 are transformed, the autocorrelation calculation section obtains 210 Autokorrelationsda RD on the basis of the body movement-eliminated pulse waveform MHj, as in the fifth embodiment. Then, the pulse state data acquisition section determines 220 on the basis of the autocorrelation data RD pulse state data ZD and the display section 230 then indicates such characters as "Ping mai", "Xuan mai" and "Hua mai" indicated by the pulse state data ZD or characters corresponding to each pulse state. The display section 230 guarantees that the person or a third party, such as a doctor, can determine the pulse status.

As previously described, the seventh embodiment is designed so that the autocorrelation data RD based on the body motion-eliminated pulse waveform MHj are obtained, excluding a body movement component is. Thus, the person's pulse state continuously in everyday life determine.

The seventh embodiment also cleverly utilizes the characteristics of body movement, with a high possibility that a component of body movement exists in a frequency zone lower than that of the frequency components of the fundamental wave of the pulse waveform MH, thereby removing the body movement component. In this embodiment, therefore, components such as the body movement detection section 20 and the waveform treatment section 21 are absent, which are required in the third and fourth embodiments, and the pulse state can be accurately detected even if there is a body movement.

Eighth Embodiment

The Autocorrelation data RD becomes in the third and fourth embodiments obtained on the basis of the pulse waveform MH and in the fifth to seventh embodiment based on the body movement-eliminated Pulse waveform MHj. In the above-mentioned wavelet transformation can Analysis data are obtained at each frequency zone, which is periodic shared. Thus, the characteristic portions of the pulse waveform are MH and body movement-eliminated Pulse waveform MHj in positive or negative peak. If these peaks appear, so does the value of the analytic data, resulting from the wavelet transformation result, in a relatively high frequency zone. If the attention is directed to a particular frequency zone, and autocorrelation data RD with respect to the analysis data in the frequency zone of interest it is therefore possible to specify the pulse state based on the autocorrelation data RD. The eighth embodiment The present invention is made in view of the above point developed.

34 FIG. 12 is a block diagram of the pulse wave examination apparatus according to the eighth embodiment. FIG. In the figure, when a pulse waveform MH passes through a pulse wave detection section 120 is detected, results in a first wavelet transform section 243 the wavelet transformation of the pulse waveform MH to obtain pulse wave analysis data MKDf corresponding to a specific frequency zone. If, for example, as in 26 That is, in the wavelet transform, when the frequency zone is divided into eight zones and the frequency zone of interest is in a range between 3.0 Hz and 2.5 Hz, M16 to M86 are output as pulse wave analysis data MKDf.

In this case, the wavelet transform section is 243 as in 35 illustrated structured. In a comparison of 35 With 4 it can be seen that the scale conversion section W2 is missing. The reason is that the scale conversion section W2 is of a type that converts the scale parameter "a" corresponding to the period, so that this function can be obtained only by storing a basic function corresponding to the frequency zone of interest in the basic function memory section W1 ,

The pulse wave analysis data MKDf obtained in this way shows a variation of the characteristic portion of the pulse waveform MH over time. Thus, the pulse waveform MH can be efficiently analyzed by calculating the autocorrelation coefficient of the pulse wave analysis data MKDf. Such an autocorrelation calculation section 210 in this embodiment, autocorrelation data RD provides the autocorrelation coefficient of the pulse wave analysis data MKDf.

Subsequently, a pulse state data acquisition section generates 220 Pulse state data ZD on the basis of the autocorrelation data RD. In this case, the pulse state data acquisition section handles 220 the autocorrelation data RD is arithmetic and compares the calculated result with a threshold value that is determined to identify the pulse state to determine the pulse state data ZD. When the pulse state data ZD becomes a display section 230 are routed, the display section shows 230 the signs "Xuan Mai", "Ping Mai" and "Hua Mai" and the like. This guarantees that the person or a third party, eg a doctor, can determine the pulse status.

9th ninth embodiment

A ninth embodiment of the present invention is applied to the pulse wave examination apparatus by using a technique that uses wavelets to remove a body movement component 1 designed the eighth embodiment.

36 is a block diagram of a pulse wave examination apparatus 1 according to the ninth embodiment. In this embodiment, a first wavelet transform section 243 and a second wavelet transform section 245 as in 35 shown constructed as in the above eighth embodiment. The first and second wavelet transform sections 243 and 245 provide pulse wave analysis data MKDf and body movement analysis data TKDf, respectively, according to a frequency zone of interest. A body movement component eliminating section 240 subtracts the body movement analysis data TKDf from the pulse wave analysis data MKDf to obtain body movement-eliminated analysis data MKDfaj.

When the body motion-eliminated analysis data MKDfaj is generated, an autocorrelation calculation section sets 210 Autocorrelation data RD showing the autocorrelation coefficient based on the body movement-eliminated analysis data MKDaj as in the eighth embodiment. Subsequently, a pulse state data acquisition section generates 220 Pulse state data ZD on the basis of the autocorrelation data RD. In this case, the pulse state data acquisition section handles 220 the autocorrelation data RD is arithmetic and compares the calculated result with a threshold configured to identify the pulse state to obtain pulse state data ZD. When the pulse state data ZD becomes a display section 230 are routed, the display section shows 230 the signs "Xuan Mai", "Ping Mai" and "Hua Mai" and the like. This guarantees that the person or a third party, eg a doctor, can determine the pulse status.

As mentioned above, in the ninth embodiment, attention is directed to a particular frequency zone and wavelet transformation is performed to eliminate a body motion component. It is therefore unnecessary to compare the results of the wavelet transform between different frequency zones. Therefore, the first and second frequency correction sections can 244 and 246 absence. Further, the autocorrelation data RD is obtained directly from the body motion-eliminated analysis data MKDfaj, so that the inverse wavelet transform section 247 can be missing.

10. Outer structure the above embodiments

Then be some examples of external structures the pulse wave examination apparatus according to the above-mentioned first to ninth embodiment of the present invention.

10.1. Kind of a wristwatch A

First, an example of the structure of a pulse wave examination apparatus will be described 1 in the manner of a wristwatch according to the above-mentioned embodiments with reference to 37A to 37C described.

As in 37A and 37B is shown comprises the device for pulse wave examination 1 predominantly a device body 100 with a wristwatch structure, a cable 101 attached to the device body 100 is connected, and a pulse wave detection section 10 which is at the side of the end of the cable 101 is arranged.

These parts become a bracelet 102 on the device body 100 attached. In particular, the bracelet 102 around the left arm of a person from the 12 o'clock direction of the device body 100 looped and the other end at a position in the 6 o'clock direction of the device body 100 attached.

Likewise, a connector portion 103 at a position in the 6 o'clock direction of the device body 100 arranged. A connector piece 104 that is the end of the cable 101 is in an unrestricted manner on the connector portion 103 attached.

If the connector piece 104 is removed, it can be seen that the connector portion 103 with an LED 113 for transmitting data and a phototransistor 114 as well as with contact pins 111 . 112 for connection to the cable 101 is provided as in 37C is shown.

On the other hand, the pulse wave detection section 10 , as in 37B at the base of a finger through a sensor attachment tape 11 attached so that it is protected from light. When the pulse wave detection section 10 attached to the base of a finger in this way, the cable can 101 be short and thus causes the pulse detection section 10 no disability, even when attached. When the distribution of body temperature from the palm to the base of a finger is measured, the temperature of the fingertip is significantly reduced even on a cold day, while the temperature at the base of the finger is relatively not reduced due to a stable blood flow rate. Therefore, when the pulse wave detection section 10 is attached to the base of a finger, a pulse waveform can be detected with accuracy even if the person goes out on a cold day.

At the side of the surface of the device body 100 is a display section 110 arranged, which is formed from a liquid crystal field. The display section 110 has a segment display zone, a dot display zone, and the like, and displays the current time, the contents of the diagnosis, and the like: the display section 110 corresponds to the notification section 80 or the display section 230 in each embodiment.

On the inside of the device body 100 An acceleration sensor, not shown, is incorporated which detects the body movement caused by the pivoting of an arm and the upward and downward movement of the body. The acceleration sensor corresponds to the body movement detection section 20 in each embodiment.

Further, on the inside of the device body 100 a CPU (not shown) which controls various calculations and transformations, and button switches SW1 and SW2 for various manipulations and display are provided on the circumference of the device body 100 arranged.

10.1.1 Detailed Structure of the pulse wave detection section

Subsequently, the structure of the pulse wave detection section becomes 10 with reference to 38 described.

As in 38 is shown, comprises the pulse wave detection section 10 an LED 12 , a phototransistor 13 and the same. When a switch SW is turned on and the supply voltage is applied, the LED is turned off 12 Light broadcast. The emitted light is reflected by the subject's blood vessel and tissue and then by the phototransistor 13 receive. The voltage that is converted by the photocurrent of the phototransistor is detected by the pulse wave detection section 10 output as MH signal.

Here is the emission wavelength of the LED 12 a wavelength near an absorption peak of hemoglobin contained in the blood is selected. The acceptance value varies depending on the blood flow rate. Therefore, a pulse waveform is detected by measuring the acceptance value.

As LED 12 For example, an InGaN (Indium Gallium Nitrogen Type) blue LED is preferably used. The emission spectrum of the blue LED has its emission peak, for example, at 450 nm, and its emission wavelength zone is in a range between 350 nm and 600 nm. As a phototransistor 13 corresponding to the LED having such emission characteristics, a GaAsP (gallium arsenic-phosphorus) type is used in this embodiment. With respect to the acceptance wavelength zone of the phototransistor 13 For example, the sensitive main zone is in a range between 300 nm and 600 nm. The phototransistor 13 also has a sensitive zone below 300 nm.

A Combination of such a blue LED and a phototransistor guarantees that a pulse wave in a wavelength range from 300 nm to 600 nm, which is the overlapping wavelength Both are captured with the following advantages.

First, of the light that is contained in extraneous light, the light having a wavelength of 700 nm or less is more likely to pass through finger tissue. Therefore, when a part of the finger which is not covered by the sensor fixing tape is irradiated with extraneous light, the light can not transmit the phototransistor reach the finger tissue, and only the light having a wavelength having no effect on the detection reaches the phototransistor 13 , On the other hand, light having a wavelength of more than 300 nm is almost absorbed at the surface of the skin, and thus, a substantial acceptance wavelength region is in the range between 300 nm and 700 nm, even if the acceptance wavelength region is below 700 nm. Therefore, the effect of extraneous light can be restricted even if the finger is not completely covered. Hemoglobin in the blood has a high absorption coefficient for light having a wavelength in the range of 300 nm to 700 nm. This absorption coefficient is many times to hundreds of times higher than that for light having a wavelength of 800 nm. Therefore, when light of one wavelength (300 nm to 700 nm) in which a high absorption coefficient is obtained when light is used for detection based on the absorption coefficient of hemoglobin, the detected value changes with high sensitivity according to the change in the blood rate. This makes it possible to improve the SN ratio of the pulse waveform MH based on a change in the blood rate.

10.2 Type of wristwatch B

Next, another example of the structure of a pulse wave examination apparatus will be described 1 with reference to 39A and 39B described. In this structure, the pulse waveform of a person is not detected photoelectrically using an LED or a phototransistor, but detected using a pressure sensor.

As in 39A is shown, the device for pulse wave examination 1 with two bands 102 provided, and a protruding elastic rubber 131 a pressure sensor 130 is on the attachment side of a fastener 120 one of the bands formed. The ribbon 102 that with the fastener 120 has a structure (the details of which are not shown) in which a flexible printed circuit (FPC) substrate is coated with a soft plastic, so that a signal coming from the pressure sensor 130 is recorded.

When using, as in 39B is shown, the device for pulse wave examination 1 with a structure in the style of a wristwatch around the left arm 150 the person looped, so that the elastic rubber 131 of the fastener 120 near a radial artery 140 is positioned. It is therefore possible to constantly detect the pulse wave. By the way, this tortuous state does not differ from that when using a normal wristwatch.

When the elastic rubber 131 near the radial artery 140 the person is pushed, there will be a change in the bloodstream (namely in the pulse wave) over the elastic gum 131 on the pressure sensor 130 transmitted and from the pressure sensor 130 recorded as blood pressure.

In addition, another example of the pulse wave detection section 10 In addition, a cuff is attached to a fingertip, and the harmonic component of the pulse wave is detected while pressure is applied to the cuff, whereby the properties of the tidal wave and the dicrotic wave can be extracted, as disclosed in Japanese Patent Application Laid-Open No. H5-192620 is described.

10.3 Kind of a necklace

It has been suggested that the device for pulse wave examination 1 is carried out in the manner of a collar according to each embodiment, as in 40 is shown.

In this figure is a pressure sensor 130 at the end of a cable 101 arranged and is near the carotid artery using an adhesive tape 170 attached, as in 41 is shown. In 40 The main parts of the device are in a device body 100 in the form of a brooch with a hollow portion, and at the front of the device body are a display portion 110 and switches SW1 and SW2 are formed. The cable 101 is partly in a chain 160 is embedded and used to supply an MH signal from the pressure sensor 130 to the device body 100 is issued.

10.4 kind of glasses

As an embodiment of the device for pulse wave examination 1 According to each embodiment, one type of spectacles is considered as in 42 is shown.

As shown in this figure, a device body is in a housing 100a and a housing 100b Divided separately on a hanger 181 the glasses are attached. The housing 100a and 100b are via a conductor wire, which is in the hanger 181 embedded, electrically connected. A liquid crystal panel 183 is on the side surface of the case 100a on the side of a lens 182 attached, and a mirror 184 is attached at one end of its side surface at a predetermined angle. The housing 100a contains a drive circuit for the liquid crystal panel 183 with a power source (not shown) and a display data providing circuit, the circuits having a display section 110 form. The light emitted by the energy source is from the mirror 184 over the liquid crystal panel 183 reflected, and on the lens 182 applied. The main parts of the device are in the housing 100b incorporated, and switches SW1 and SW2 are, as in the previous embodiment, on the housing 100b educated.

A pressure sensor 130 is over a cable 101 electrically to the housing 100b attached and attached as in the case of the necklace near the carotid artery. It is noted that the lead wire, which is the case 100a with the housing 100b joins, along the temple 181 can be performed. Although in this example the device body in the housing 100a and 100b divided, these housings can also be formed into a unitary housing. Furthermore, the mirror 184 be movable to the angle with the liquid crystal panel 183 adjust.

10.5 Kind of a card

As another embodiment of the device for pulse wave examination 1 According to each embodiment, the type of card is considered as in 43 is shown. A device body 100 in the manner of a card is housed, for example, in the left breast pocket of a person. A pressure sensor 130 is over a cable 101 electrically to the device body 100 attached, and is attached near the carotid artery as in the case of the necklace and the glasses.

10.6 Type of pedometer

As another embodiment of the device for pulse wave examination 1 According to each embodiment, the kind of a pedometer is considered as in FIG 44A is shown. As in 44B is a device body 100 in the manner of a pedometer on a waist belt 191 attached. A pressure sensor 130 is over a cable 101 electrically to the device body 100 connected, and is attached near the femoral beating vein in the hip joint of a person using an adhesive tape, and by a holder 192 protected. In this case, measures are taken as desired, so that the cable 101 is sewn into garments so that it does not hinder the daily life of the person.

Tenth embodiment

11.1 Theoretical basis the tenth embodiment

47 Fig. 10 shows a structure that the inventors of the present invention use to record a waveform of arterial pressure in the radial artery. A continuous blood pressure monitor 580 (CMB-2000, manufactured by COLIN CORPORATION) as in 47 includes a wristband blood pressure measurement section 582 , a spoke arterial sensor section 584 , a control section 586 to control these sections, and a personal computer 588 who is at the control section 586 connected.

48 Fig. 12 is a graph showing a typical arterial pressure waveform, namely, a waveform of a blood pressure in the radial artery measured by such a device as mentioned above. The waveform of blood pressure in the artery is as in 48 in general, provided with a highest peak ejection wave, a tidal wave with the next peak, and a dicrotic wave with the third peak. The peak of the ejection wave corresponds to a systolic blood pressure BP _sys . Diastolic blood pressure BP _dir corresponds to the lowest blood pressure in the blood pressure waveform. A pressure difference between the systolic blood pressure BP _sys and the diastolic blood pressure BP _dir is referred to as the pulse pressure ΔBP. The mean blood pressure BP _mean is obtained by integrating the waveform of the blood pressure and calculating the time average of the resulting value.

In the continuous blood pressure monitor 580 who in 47 is shown, the bracelet blood pressure measuring section 582 used for measuring systolic blood pressure BP _sys and diastolic blood pressure BP _dir . The radial arterial sensor section 584 detects a pulse waveform corresponding to the waveform of the Corresponds to blood pressure in the radial artery. This pulse waveform is calibrated by the systolic blood pressure BP _sys and the diastolic blood pressure BP _{dir obtained} from the wrist blood pressure measurement section 582 are measured to obtain a waveform of arterial pressure.

Using the continuous blood pressure monitor 580 The inventors of the present invention measured the waveform of blood pressure in each radial artery of 74 healthy adults, aged 22 to 46 years, at a time when they were hungry (09: 30-13: 30), while after a resting period of 15 Minutes sat.

49 to 51 Fig. 11 are graphs showing the results plotted for data obtained by such measurement. 49 shows that there is a strong linear relationship between the mean blood pressure BP _mean and the diastolic blood pressure BP _dir , with a strong correlation with a correlation coefficient r of 0.95. 50 shows that there is also a strong linear relationship between the mean blood pressure BP _mean and the systolic blood pressure BP _sys (correlation coefficient r = 0.87). Further shows 51 in that it also gives a strong linear relationship between the pulse pressure ΔBP, which is the pressure difference between the systolic blood pressure BP _sys and the diastolic blood pressure BP _dir , and the systolic blood pressure BP _sys (correlation coefficient r = 0.76). It is therefore clear that the blood pressure can be expressed by the mean blood pressure BP _mean or the pulse pressure Δ BP.

11.2 Structure of the blood pressure monitor

52 is a block diagram showing the structure of a blood pressure monitor 500 this embodiment shows. As shown in this figure, the blood pressure monitor includes 500 a detection section of the arterial pressure waveform 504 , a blood pressure conversion section 516 , a calculation section of the mean blood pressure 508 a pulse pressure calculating section 512 , a blood pressure judgment information storage section 520 , a blood pressure judging section 524 and an output section 528 ,

A detection section of the arterial pressure waveform 504 continuously measures the blood pressure in an artery to detect a waveform of arterial pressure. The detection section of the arterial pressure waveform 504 For example, with a radial arterial sensor section 584 , in 47 shown, a pulse wave detection section 10 , in 37B represented, and a pressure sensor 130 , in 39A . 40 . 41 . 42 . 43 and 44A represented, be formed.

The blood pressure conversion section 516 converts the arterial pressure waveform coming from the arterial pressure waveform detection section 504 is detected in the waveform of the arterial pressure at the cardiac position at a position corresponding to the height of the heart. For example, the blood pressure conversion section includes 516 calibrating the arterial pressure waveform from the arterial pressure waveform detecting section 504 is detected using a maximum blood pressure and a minimum blood pressure detected by a wrist blood pressure monitor.

The calculation section of the mean blood pressure 508 calculates the mean blood pressure BP _mean on the basis of the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

The pulse pressure calculation section 512 calculates the pulse pressure ΔBP which is the pressure difference between a maximum pressure (the systolic blood pressure BP _sys ) and a minimum pressure (the diastolic blood pressure BP _sir ) on the basis of the waveform of the arterial pressure.

The blood pressure judgment information storage section 520 stores blood pressure evaluation information in advance. These blood pressure judgment information include, for example, a threshold value of blood pressure, in terms of mean blood pressure and pulse pressure, which is a borderline blood pressure between positive pressure and normal pressure, and a threshold value of blood pressure, which is a borderline blood pressure between negative pressure and normal blood pressure. Needless to say, the mean blood pressure and the pulse pressure have high correlations with the systolic blood pressure BP _sys (maximum blood pressure) and the diastolic blood pressure BP _dir (minimum blood pressure) and become the index indicating the condition of the blood pressure as before with reference to 49 to 51 was mentioned.

The blood pressure judgment section 524 judges the blood pressure on the basis of at least one of the mean blood pressure BP _mean and the pulse pressure ΔBP and the blood pressure judgment information included in the blood pressure judgment information storage section 520 are stored. For example, a Judgment as to whether it is overpressure, negative pressure or normal pressure based on at least one of the obtained mean blood pressure BP _mean and the pulse pressure ΔBP and the blood pressure judgment information.

The output section 528 It outputs at least one kind of information corresponding to the mean blood pressure BP _mean , the pulse pressure ΔBP and the judgment of the blood pressure. The output section 528 indicates at least one kind of information corresponding to the average blood pressure, information corresponding to the pulse pressure, and information corresponding to the judgment of the blood pressure to either a liquid crystal display, a CRT, a printer or the like in the form of, for example, numbers and Graphics or as tensions or digital information that matches any type of information.

11.3 Operation of the Blood Pressure Monitor

The functioning of the blood pressure monitor 500 This embodiment will be described with reference to 52 described.

First, the detection section measures the arterial pressure waveform 504 the blood pressure in the artery continuously using the above-mentioned pressure sensor 130 or the like to detect a waveform of the arterial pressure.

The waveform of the arterial pressure supplied by the arterial pressure waveform detecting section 504 is detected by the blood pressure conversion section 516 converted into the waveform of the arterial pressure at the cardiac position, which is a waveform of arterial pressure at a position corresponding to the height of the heart.

Subsequently, the calculation section calculates the mean blood pressure 508 the mean blood pressure BP _mean on the basis of the waveform of the arterial pressure of the waveform of the arterial pressure at the cardiac position detected by the detection portion of the arterial pressure waveform 504 or the blood pressure conversion section 516 be issued.

At the same time, the pulse pressure calculation section calculates 512 the pulse pressure ΔBP, which is the pressure difference between a maximum blood pressure (systolic blood pressure BP _sys ) and a minimum blood pressure (diastolic blood pressure BP _dir ) based on the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position derived from the Detection section of the arterial pressure waveform 504 or the blood pressure conversion section 516 be issued.

Then, at least one of the mean blood pressure BP _mean and the pulse pressure ΔBP becomes the blood pressure judging section 524 entered. The blood pressure judgment section 524 determines whether it is, for example, a positive pressure, negative pressure or normal pressure, on the basis of the input data and the blood pressure judgment information included in the blood pressure judgment information storage section 520 are stored.

The output section 528 outputs at least one kind of information corresponding to the mean blood pressure BP _mean , information corresponding to the pulse pressure ΔBP, and information corresponding to the judgment of the blood pressure. The output section is provided with, for example, a liquid crystal display, a CRT, a printer, or the like, and can output any type of information in the form of, for example, numbers and graphics, or as voltages or digital information corresponding to each type of information.

That way, the blood pressure monitor can 500 of this embodiment, the average blood pressure and the pulse pressure based on the waveform of the arterial pressure, that of the detection portion of the arterial pressure waveform 504 is recorded, calculated and monitored. The blood pressure monitor 500 Also, on the basis of at least one of the obtained mean blood pressure BP _mean and the pulse pressure ΔBP and the blood pressure judgment information stored in advance, it may make a determination as to whether it is an over-pressure, under-pressure or normal pressure.

Eleventh Embodiment

12.1. Theoretical basis the eleventh embodiment

The Invention of the present invention further resulted in the following Experiment using the data in the experiment obtained in the section "Theoretical Basis of the Tenth Embodiment".

More specifically, the obtained arterial artery pressure waveforms in Pingmai, Hua mai, and Xuan may have their typical arterial pressure waveforms in FIG 45A . 45B and 45C Classified as referring to the waveform model of Chinese medicine waveforms (Kobe Research Institute of Chinese Medicine: Tongue Diagnosis and Pulse Diagnosis in Chinese Medicine Diagnosis, Fei Zhaofu (Editor), Shanghai Chinese medical college publishing house (1991)).

As a result, it was confirmed that, as in 53 Hua Mai, Ping Mai and Xuan Mai are significantly affected by the dicrotic wave height ΔBP _D (see 48 ), which is a difference in blood pressure between the dicrotic notch and a tip of a dicrotic wave. In particular, ΔBP _D of Hua mai was 11 ± 4 mmHg, ΔBP _D of Ping mai was 7 ± 2 mmHg, and ΔBP _D of Xuan may was 3 ± 1 mmHg, showing a significant difference between the three groups with a significance level of 1%.

54 shows that there is a linear relationship between the dicrotic pressure difference ratio BP _Dd / ΔBP and the dicrotic wave height ΔBP _D , where the ratio BP _Dd / ΔBP is the ratio of the dicrotic pressure difference BP _Dd (see FIG 48 ), which is the pressure difference between the blood pressure at a dicrotic notch and the minimum blood pressure, to the pulse pressure ΔBP, which is the pressure difference between the maximum blood pressure and the minimum blood pressure. The correlation coefficient between the two is -0.86, indicating a strong correlation. Therefore, it is clear that the dicrotic pressure difference ratio BP _Dd / ΔBP can be used as an index for the significant classification of Hua mai, Ping mai and Xuan may, which are the typical pulse waveforms in pulse diagnosis used in Chinese medicine.

55 shows that there is a linear relationship between the diastolic effusion pressure ΔBP _P , which is the pressure difference between the blood pressure at a dicrotic notch and the maximum blood pressure, and the dicrotic wave height ΔBP _D. The correlation coefficient between them is 0.77, indicating a strong correlation. The diastolic effusion pressure ΔBP _P can also be used as an index for the significant classification of Hua mai, Ping mai and Xuan may, which are the typical pulse waveforms in the pulse diagnosis used in Chinese medicine.

As further out 45A . 45B and 45C 1, showing typical waveforms of arterial pressure in pulse waveforms classified into Ping mai, Hua mai, and Xuan may be detected in the pulse diagnosis used in Chinese medicine, the ratio of the mean blood pressure BP _mean to that increases Pulse pressure ΔBP, namely the mean blood pressure-pulse pressure ratio BP _mean / ΔBP in the order Hua mai, Ping mai and Xuan may. It is therefore possible to classify pulse waveforms, namely Hua mai, Ping mai and Xuan may by the mean blood pressure-pulse pressure ratio BP _mean / ΔBP.

12.2. Structure of the pulse waveform monitor

56 is a block diagram showing the structure of a pulse waveform monitor 540 this embodiment shows. As in 56 is shown includes the pulse waveform monitor 540 a detection section of the arterial pressure waveform 504 , a calculation section of the dicrotic wave height 554 , a calculating portion of the dicrotic pressure difference ratio 548 , a calculation section of the mean blood pressure pulse pressure 552 , a calculation section of diastolic effusion pressure 554 , a pulse waveform judgment information storage section 556 , a pulse waveform judging section 560 and an output section 564 , It is stated that, although in 56 not shown, a blood pressure conversion section after the detection section of the arterial pressure waveform 504 and before the dicrotic wave height calculation section 544 , the calculating section of the dicrotic pressure difference ratio 548 and the calculation section of the mean blood pressure pulse pressure 552 can be arranged.

The detection section of the arterial pressure waveform 504 measures the blood pressure in the artery konti to detect a waveform of arterial pressure. The detection section of the arterial pressure waveform 504 can with a radial arterial sensor section 584 , as in 47 shown, a pulse wave detection section 10 , as in 37B represented, and a pressure sensor 130 , as in 39A . 40 . 41 . 42 . 43 and 44A be formed.

The blood pressure conversion section 516 converts the waveform of the arterial pressure that is derived from the detection section of the arterial pressure waveform 504 is detected in the waveform of the arterial pressure at the cardiac position at a height corresponding to the heart.

The calculation section of the dicrotic wave height 544 calculates the dicrotic wave height ΔBP _D (see 48 ), which is the difference in blood pressure between the dicrotic notch and the tip of a dicrotic wave, based on the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

The calculation section of the dicrotic pressure difference ratio 548 calculates the dicrotic pressure difference ratio BP _Dd / ΔBP which is the ratio of the dicrotic pressure difference BP _Dd , which is the pressure difference between the blood pressure at a dicrotic notch and the minimum blood pressure (the diastolic blood pressure BP _dir ) to the pulse pressure ΔBP, which is the pressure difference is between the maximum blood pressure and the minimum blood pressure, based on the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

The calculation section of the mean blood pressure-pulse pressure ratio 552 calculates the mean blood pressure pulse pressure ratio BP _mean / ΔBP, which is the ratio of the mean blood pressure BP _mean to the pulse pressure ΔBP, which is the pressure difference between the maximum blood pressure and the minimum blood pressure based on the waveform of the arterial pressure or the waveform of the arterial pressure at the heart position.

The Calculation Section of Diastolic Effusion Pressure ΔBP _P - 554 calculates the diastolic effusion pressure ΔBP _P (see 48 ), which is the difference between the blood pressure at a dicrotic notch and the systolic blood pressure BP _{sys obtained} from the pulse wave of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

The pulse waveform judgment information storage section 556 stores pulse waveform judgment information in advance. The pulse waveform judgment information includes, for example, threshold values for the dicrotic wave height ΔBP _D , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, or the diastolic effusion pressure ΔBP _P to classify pulse waveforms, for example, Hua mai, Pingmai and Xuan may, which are typical pulse waveforms in pulse diagnosis used in Chinese medicine. These pulse waveforms may be sorted by the dicrotic wave height ΔBP _d , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, or the diastolic effusion pressure ΔBP _P as described above with reference to FIG 53 . 54 . 45A . 45B . 45C and 55 was mentioned.

The pulse waveform judgment section 560 judges the pulse waveform on the basis of the pulse waveform judgment information and at least one of the dicrotic wave height ΔBP _D , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, and the diastolic effusion pressure ΔBP _P. It is therefore possible, for example, Hua mai, Ping mai and Xuan mai, which show pulse waveforms in the pulse diagnosis used in Chinese medicine, to judge by the pulse waveform judgment information stored in advance and by at least one of the dicrotic one Wave height ΔBP _d , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP or the diastolic effusion pressure ΔBP _P.

The output section 564 outputs at least one kind of information corresponding to the dicrotic wave height ΔBP _D, the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure-pulse pressure ratio BP _mean / ΔBP, the effusion diastolic pressure ΔBP _P and the pulse waveform-judging information. This information may be output to either a liquid crystal display, a CRT or a printer in the form of numbers or characters, or as voltage or digital information corresponding to the information.

12.3. Functioning of the Pulse waveform monitor

The operation of the pulse waveform monitor 540 This embodiment will be described with reference to 56 described.

First, the detection section measures the arterial pressure waveform 504 the blood pressure in the artery continuously through the above-mentioned pressure sensor 130 or the like to detect a waveform of the arterial pressure.

Then, the blood pressure converting section converts the waveform of the arterial pressure received from the arterial pressure waveform detecting section 504 was detected in the waveform of the arterial pressure at the cardiac position at a position corresponding to the height of the heart. It is noted that this step may be absent when the arterial pressure waveform is used in the following steps.

Subsequently, the calculation section calculates the dicrotic wave height 544 the dicrotic wave height ΔBP _D (see 48 ), which is the difference in blood pressure between the dicrotic notch and the tip of a dicrotic wave, based on the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

In parallel to the calculations of the dicrotic wave height ΔBP _D , the calculation section calculates the dicrotic pressure difference ratio 548 the dicrotic pressure difference ratio BP _Dd / ΔBP, which is the ratio of the dicrotic pressure difference BP _Dd , which is the pressure difference between the blood pressure at a dicrotic notch and the minimum blood pressure (the diastolic blood pressure BP _dir ), to the pulse pressure ΔBP, which is the pressure difference between a maximum blood pressure and a minimum blood pressure, based on the waveform of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

At the same time, the calculation section calculates the mean blood pressure-pulse pressure ratio 552 the mean blood pressure pulse pressure ratio BP _mean / ΔBP which is the ratio of the mean blood pressure BP _mean to the pulse pressure ΔBP which is the pressure difference between the maximum blood pressure and the minimum blood pressure on the basis of the arterial pressure waveform or the arterial waveform Pressure at the heart position.

In parallel with the above-mentioned calculations, the calculating portion of the diastolic effusion pressure ΔBP _P also calculates 554 the diastolic effusion pressure ΔBP _P (see 48 ), which is the difference between the blood pressure at a dicrotic notch and the systolic blood pressure BP _{sys obtained} from the pulse wave of the arterial pressure or the waveform of the arterial pressure at the cardiac position.

Then, the pulse waveform judging section judges 560 the pulse waveform such as Hua mai, Ping mai, and Xuan may represent pulse waveforms in the pulse diagnosis used in Chinese medicine on the basis of the pulse waveform judgment information and at least one of the dicrotic wave height ΔBP _D , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, and the diastolic effusion pressure ΔBP _P.

The output section 564 outputs at least one kind of information corresponding to the dicrotic wave height ΔBP _D, the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure-pulse pressure ratio BP _mean / ΔBP, the effusion diastolic pressure ΔBP _P and the pulse waveform-judging information. This information may be output to either a liquid crystal display, a CRT or a printer in the form of numbers or characters, or as voltage or digital information corresponding to the information.

In this way, according to the pulse waveform monitor 540 this embodiment of at least one of the dicrotic wave height ΔBP _d , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, and the diastolic effusion pressure ΔBP _P based on the waveform of the arterial pressure detected by the arterial pressure detection section pressure waveform 504 is calculated. The pulse waveform monitor 540 may also judge the pulse waveform based on at least one of the dicrotic wave height ΔBP _d , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP, and the diastolic effusion pressure ΔBP _P and the pulse waveform judgment information. The pulse waveform monitor 540 Further, one kind of information may be the dicrotic wave height ΔBP _d , the dicrotic pressure difference ratio BP _Dd / ΔBP, the mean blood pressure pulse pressure ratio BP _mean / ΔBP and the diastolic effusion pressure ΔBP _P and output information related to the pulse waveform in the form of, for example, numbers, graphics, or voltages.

13. Twelfth embodiment

13.1 Principle

The inventors of the present invention monitored the above-mentioned diastolic effusion pressure ΔBP _P , namely, the difference between the blood pressure at a dicrotic notch and the systolic pressure obtained from the waveform of the arterial pressure and the dicrotic wave height ΔBP _D , namely, the difference in blood pressure of the dicrotic notch and the tip of the dicrotic wave, using a pulse waveform monitor having the same structure as the pulse waveform monitor used in the eleventh embodiment. As a result, it has been confirmed that administration of certain types of medication, for example, a hypotensive agent, results in a change in diastolic effusion pressure, as shown below.

63 FIG. 13 is a graph showing the results of the mean blood pressure BP _mean , the diastolic effusion pressure ΔBP _P , the dicrotic pressure difference BP _Dd , which is the pressure difference between the blood pressure at the dicrotic notch and the minimum blood pressure, and the dicrotic wave height ΔBP _D representing the Difference in blood pressure between the dicrotic notch and the tip of the dicrotic shaft is shown in a period between 60 minutes before administration and 60 minutes after the administration when nifezipin is administered as a hypotensive agent at time 0 (minutes). In figure In 64 For example, the waveform called "control" is a waveform of the arterial pressure of a beat as an average for 60 minutes before the administration of the hypotensive agent, and the waveform designated as "Nf" is a waveform of the arterial pressure of one Beat as an average for 10 seconds 15 minutes after administration of the hypotensive agent. It can be clearly seen from these figures that the administration of the hypotensive agent leads to a decrease in the mean blood pressure BP _mean , an increase in the diastolic effusion pressure ΔBP and an increase in the dicrotic wave height ΔBP _D. This embodiment relates to a pharmacological activity monitor constructed on the basis of the result of observing such a pharmacological action.

13.2 Structure and functioning of the pharmacological impact monitor

A pharmacological impact monitor 570 , as in 57 is not shown with the dicrotic pressure difference ratio calculation section 548 and the calculation section of the mean blood pressure-pulse pressure ratio 552 provided in the pulse waveform monitor 540 are provided, which is shown in the eleventh embodiment. In the pharmacological impact monitor 570 becomes a judging section of the pharmacological action 574 instead of the pulse waveform judging section, and a storage section of the pharmacological effect judgment information 572 is used in place of the pulse waveform judgment information storage section. The pharmacological impact monitor 570 has the same structure as the pulse waveform monitor 540 the eleventh embodiment except for the above-mentioned portions.

If in the pharmacological impact monitor 570 With such a structure, the detection portion of the arterial pressure waveform 504 When a waveform of the arterial pressure is detected, the information about the waveform becomes a calculating portion of the diastolic effusion pressure 554 and a dicrotic wave height calculating section 544 entered. The Calculation Section of Diastolic Effusion Pressure 554 calculates the diastolic effusion pressure, which is the difference between the systolic blood pressure (maximum blood pressure) and the dicrotic blood pressure, and outputs the diastolic effusion pressure to the judging section of the pharmacological action 574 and to an output section 564 out. The calculation section of the dicrotic wave height 544 calculates a dicrotic wave height, which is the difference in blood pressure between the dicrotic notch and the tip of a dicrotic wave, and supplies the calculated data to the pharmacological action judging section 574 and to the output section 564 out.

The evaluation section of the pharmacological action 574 judges the pharmacological action according to the input data of the diastolic effusion pressure and the dicrotic wave height on the basis of the pharmacological performance evaluation information included in the memory portion of the pharmacological effect evaluation information 572 are stored, and outputs the result to the output section 564 out. The output section 564 gives the values of diastolic effusion pressure and dicrotic Wave height and the result judged by the pharmacological effect judging section, for example, as image information on an LCD, as sound information from a speaker and in the form of a voltage.

In the pharmacological impact monitor 570 That is, a pulse wave detection section for detecting a pulse waveform, which is a wave of blood output from the heart and flowing through a blood vessel, may be used instead of the detection section of the arterial pressure waveform 504 be used. In this case, the calculation section of diastolic effusion pressure 554 and the calculating section of the dicrotic wave height 544 do not calculate the absolute blood pressure. Thus, they can be replaced by the diastolic effusion pressure ratio calculating section and the dicrotic wave height ratio calculating section to calculate a diastolic effusion pressure ratio and a dicrotic wave height ratio normalized by the pulse pressure, namely, the difference between the systolic pressure and the diastolic pressure, respectively that a data comparison can be performed exactly.

In this embodiment, the pharmacological activity monitor 570 with the calculation section of diastolic effusion pressure 554 and the dicrotic wave height calculating section 544 provided. However, a pharmacological effect monitor may have a structure in which at least one of the calculating portion of the diastolic effusion pressure 554 and the dicrotic wave height calculating section 544 is used.

14. Others modifications

• (1) In der vorangehenden ersten Ausführungsform ermittelt der Extrahierabschnitt für die tidale Welleneigenschaft 50 die tidalen Welleneigenschaftsdaten TWD durch (f2 + f3 + f4)/f1 und der Extrahierabschnitt für die dikrote Welleneigenschaft 60 ermittelt die dikroten Welleneigenschaftsdaten DWD durch (f5 + f6 + f7)/f1. Die vorliegende Erfindung ist nicht auf das Vorhergesagte beschränkt, und diese Abschnitte können die Eigenschaften der tidalen Welle und dikroten Welle auf der Basis jeder harmonischen Komponente extrahieren, insofern als die harmonische Komponente das Extrahieren der Eigenschaften der tidalen Welle und der dikroten Welle ermöglicht.
• (2) In der vorangehenden zweiten Ausführungsform werden die Zeitpositionen der tidalen Welle und dikroten Welle auf der Basis der Pulswellenanalysedaten MKD spezifiziert. Die vorliegende Erfindung ist jedoch nicht auf das Vorhergesagte beschränkt, sondern es kann jedes Verfahren angewendet werden, insofern es jede Zeitposition spezifizieren kann. Zum Beispiel wird das MHj Signal differenziert, um seinen Nulldurchgangspunkt zu berechnen, um dadurch den Spitzenpunkt des MHj Signals zu bestimmen, durch den die Zeitpositionen der tidalen welle und der dikroten Welle spezifiziert sind.
• (3) In der vorangehenden zweiten Ausführungsform wird die Frequenzanalyse des MHj Signals vorgenommen, indem eine Wavelet-Transformation ausgeführt wird. Es kann ein Verfahren angewendet werden, in dem eine Fensterfunktion zum Extrahieren einer tidalen Welle und einer dikroten Welle aus dem MHj Signal verwendet wird, und die extrahierte tidale Welle und dikrote Welle jeweils einer FFT-Behandlung unterzogen werden.
• (4) In der ersten und zweiten Ausführungsform wird, wie zuvor erwähnt, eine Frequenzanalyse durch FFT-Behandlung (erste Ausführungsform) und eine Zeit-Frequenz-Analyse durch die Wavelet-Transformation (zweite Ausführungsform) ausgeführt, um die Eigenschaften einer tidalen Welle und dikroten Welle zu extrahieren. Die vorliegende Erfindung ist jedoch nicht auf das Vorhergesagte beschränkt, sondern es können jegliche Maßnahmen ergriffen werden, insofern diese Eigenschaften auf der Basis der Amplituden einer tidalen Welle und einer dikroten Welle extrahiert werden können. Zum Beispiel kann ein Verfahren angewendet werden, in dem das MHj Signal einer Zwei-Stufen-Differenzierung unterzogen wird, um die Spitze des MHj Signals zu verstärken, und die Amplituden der tidalen Welle und dikroten Welle werden auf der Basis des erhaltenen Signals berechnet, wodurch jede der Amplituden als Eigenschaften jeder Welle extrahiert wird.
• (5) In der sechsten und siebenten, oben erwähnten Ausführungsform werden der erste Frequenzkorrekturabschnitt und der zweite Frequenzkorrekturabschnitt verwendet. Diese Strukturen können jedoch fehlen.
• (6) Die Wavelet-Transformation und die inverse Wavelet-Transformation, die in den vorangehenden Ausführungsformen beschrieben sind, können unter Verwendung einer Filterbank ausgeführt werden. 58 zeigt ein Beispiel der Struktur einer Filterbank, die in der Wavelet-Transformation verwendet wird. In der Figur ist die Filterbank in drei Stufen strukturiert und ihre Basiseinheit besteht aus einem Hochfrequenzfilter 1A und einem Dezimationsfilter 1C und einem Niederfrequenzfilter 1B und einem Dezimationsfilter 1C. Das Hochfrequenzfilter 1A und das Niederfrequenzfilter 1B teilen einen bestimmten Frequenzbereich, um eine Hochfrequenzkomponente beziehungsweise eine Niederfrequenzkomponente auszugeben. Da angenommen wird, dass der Frequenzbereich der Pulswellendaten MD im Bereich zwischen 0 Hz und 4 Hz in dieser Ausführungsform liegt, ist der Durchlassbereich des Hochfrequenzfilters 1A der ersten Stufe so konstruiert, dass er im Bereich zwischen 2 Hz und 4 Hz liegt, während der Durchlassbereich des Niederfrequenzfilters 1B der ersten Stufe so konstruiert ist, dass er im Bereich zwischen 0 Hz und 2 Hz liegt. Das Dezimationsfilter 1C dünnt Daten bei jeder Abtastung aus.

Various modifications may be made in the embodiments of the present invention.

• (1) In the foregoing first embodiment, the tidal wave characteristic extracting section detects 50 the tidal wave characteristic data TWD by (f2 + f3 + f4) / f1 and the dicrotic wave property extracting section 60 obtains the dicrotic wave property data DWD by (f5 + f6 + f7) / f1. The present invention is not limited to the above, and these portions can extract the properties of the tidal wave and the dicrotic wave on the basis of each harmonic component insofar as the harmonic component makes it possible to extract the properties of the tidal wave and the dicrotic wave.
• (2) In the foregoing second embodiment, the time positions of the tidal wave and the dicrotic wave are specified on the basis of the pulse wave analysis data MKD. However, the present invention is not limited to the above, but any method can be used insofar as it can specify each time position. For example, the MHj signal is differentiated to calculate its zero crossing point to thereby determine the peak point of the MHj signal by which the time positions of the tidal wave and the dicrotic wave are specified.
• (3) In the foregoing second embodiment, the frequency analysis of the MHj signal is performed by performing a wavelet transform. A method may be adopted in which a window function for extracting a tidal wave and a dicrotic wave from the MHj signal is used, and the extracted tidal wave and dicrotic wave are each subjected to FFT treatment.
• (4) In the first and second embodiments, as previously mentioned, frequency analysis by FFT treatment (first embodiment) and time-frequency analysis by the wavelet transform (second embodiment) are performed to evaluate the properties of a tidal wave and Extract dicrotic wave. However, the present invention is not limited to the above, but any measures can be taken as far as these characteristics can be extracted on the basis of the amplitudes of a tidal wave and a dicrotic wave. For example, a method may be employed in which the MHj signal is subjected to two-stage differentiation to amplify the peak of the MHj signal, and the amplitudes of the tidal wave and the dicrotic wave are calculated on the basis of the obtained signal, thereby each of the amplitudes is extracted as properties of each wave.
• (5) In the sixth and seventh embodiments mentioned above, the first frequency correction section and the second frequency correction section are used. However, these structures may be missing.
• (6) The wavelet transform and the inverse wavelet transform described in the foregoing embodiments may be performed using a filter bank. 58 shows an example of the structure of a filter bank used in the wavelet transform. In the figure, the filter bank is structured in three stages and its base unit consists of a high-frequency filter 1A and a decimation filter 1C and a low frequency filter 1B and a decimation filter 1C , The High frequency filter 1A and the low frequency filter 1B divide a certain frequency range to output a high frequency component and a low frequency component, respectively. Since it is assumed that the frequency range of the pulse wave data MD is in the range between 0 Hz and 4 Hz in this embodiment, the pass band of the high-frequency filter is 1A the first stage is designed to be in the range between 2 Hz and 4 Hz, while the pass band of the low frequency filter 1B the first stage is designed to be in the range between 0 Hz and 2 Hz. The decimation filter 1C thins data at each scan.

If the data that is determined in this way, to the next stage is passed, the division of the frequency range and the data thinning process repeated to the frequency range between 0 Hz and 4 Hz in eight Divide zones, thereby obtaining data M1 to M8.

The high frequency filter 1A and the low frequency filter 1B may be formed of a transversal filter including a delay element (D flip-flip) inside. Incidentally, the human pulse rate ranges from 40 to 200, and the frequency of the fundamental wave of the pulse waveform MH changes every moment according to the state of a living body. In this case, therefore, if the divided frequency range is made to change in synchronization with the frequency of the fundamental wave, information following the state of a dynamic living body can be obtained. For this purpose, the divided frequency zone can be varied accordingly by passing the pulse waveform MH as a clock signal to the transversal filter.

Of the pulse wave analysis data MKD, typical frequency components showing the characteristics of the pulse waveform MH are each frequency component of the fundamental wave, the second harmonic wave, and the third harmonic wave. The pulse state may be determined using a portion of the data M * 1 to M * 8 output from the filter bank. In this case, if the filter bank is structured to synchronize with the pulse waveform MH as mentioned above, a part of the high-frequency filter 1A , Low frequency filter 1B and decimation filters 1C be omitted, so that the structure can be simplified.

Subsequently shows 59 an example of the structure of an inverse filter bank used to perform the inverse wavelet transform. In the figure, the filter bank has a three-stage structure, wherein the base unit consists of a high-frequency filter 2A and an interpolation filter 2C , a low-frequency filter 2 B and an interpolation filter 2C and an adder. The high frequency filter 2A and the low frequency filter 2 B each divide a prescribed frequency range to output a high frequency component and a low frequency component, respectively. The interpolation filter 2C interpolates one sample of every two samples.

Here, it is necessary to reproduce a waveform, a complementary reconstruction filter bank in the filter bank, which in 58 is shown, and in the filter bank, in 59 is shown to use. In this case, the following relationship between the characteristics of the high-frequency filter 1A . 2A and the low frequency filters 1B . 2 B getting produced. H0 (-Z) F0 (Z) + H1 (-Z) F1 (Z) = 0 H0 (Z) F0 (Z) + H1 (-Z) F1 (Z) = 2Z -L

• (7) In den obengenannten Ausführungsformen ist der Anzeigeabschnitt 30 als Beispiel einer Maßnahme zur Ausgabe von Informationen dargestellt. Als Beispiel für Maßnahmen zur Information von Personen über eine Vorrichtung können als Alternative jene angeführt werden, die in der Folge beschrieben sind. Es wird als angemessen angesehen, dass diese Maßnahmen nach einem Standard klassifiziert werden können, der auf den fünf Sinnen beruht. Diese Maßnahmen können natürlich nicht nur einzeln, sondern auch in Kombinationen aus einer Mehrzahl von Maßnahmen verwendet werden. Zusätzlich ermöglicht die Verwendung von Maßnahmen, die sich an die fünf Sinne richten, die nicht der Sehsinn sind, dass sogar sehbehinderte Personen die Informationen verstehen können. Ebenso ermöglichen die Maßnahmen die sich an die fünf Sinne richten, die nicht der Hörsinn sind, dass Personen benachrichtigt werden, die gehörgeschädigt sind. Somit kann eine Vorrichtung bereitgestellt werden, die selbst für behinderte Personen benutzerfreundlich ist.

The high frequency filter 2A and the low frequency filter 2 B may consist of a transversal filter containing a delay element (D-flip-flip) inside. When a clock signal to be supplied is synchronized with the pulse waveform MH to make the divided range variable in synchronism with the frequency of the fundamental wave of the pulse waveform MH in the filter bank included in the wavelet transform section 10 is used, the clock signal to the high-frequency filter 2A and to the low frequency filter 2 B be directed.

• (7) In the above embodiments, the display section is 30 presented as an example of a measure to output information. As an example of measures for informing people about a device, as an alternative may be cited those described below. It is considered appropriate that these measures can be classified according to a standard based on the five senses. Of course, these measures can not only be used individually but also in combinations of a plurality of measures. In addition, the use of measures directed to the five senses, which are not the sense of sight, allows even visually impaired people to understand the information. Likewise, the measures that can be addressed to the five senses, which are not the sense of hearing, to alert people who are hearing impaired. Thus, a device can be provided which is user-friendly even for disabled persons.

First, include Notification devices that relate to the sense of hearing, those that either the Communicate results of analysis and diagnosis of cardiac function or issue a warning. For example, these funds are through piezoelectric elements and speakers, as well as buzzer shown. To give a specific example, is an idea that a person to be notified near a portable radio receiver carries with itself and on this receiver is accessed from the side of the device when a notification should be done. There is also a notification using of these devices many cases in which not only a simple notification takes place, but also some extra Information to be communicated. In this case, the information level as mentioned below, for example the sound volume, changed become. These types of information include pitch, sound volume, Tone color, voice, type of music (programs).

Secondly is the purpose of using the notification tool, which is refers to the sense of sight, the communication of various messages and the results of the measurements, or the issuing of a warning of one Contraption. The following devices are considered suitable for the above purposes. In particular, examples are for the Display devices CRTs (cathode tube displays), LCDs (liquid crystal displays), Printer, XY writer and lamps. A projector in the style of glasses is an example for one specific display device. In the notification, the considered in the following variations.

These variations include, for example, a distinction in display between a digital display and an analog display in the representation of numbers, a display by graphics, the concentration of a display color, and a display by a bar graph, pie chart, or face table in the case of transmission of Numbers themselves or as graduated numerals. An example of the facial table is in 60 shown.

Then, the use of tactile notification means may be considered for the purpose of warning. The following measures are taken to accomplish the above purposes: electrical stimulation generated by exciting a shape memory alloy projecting from the back of a portable device such as a wristwatch, and mechanical stimulation provided by an appendage extending in one portable device such as a wristwatch is formed so that it can move freely in and out of the back of the device, or by the vibration of a device body (for example, the device body 100 ) of a wristwatch.

In addition, can a notification means relating to the sense of smell, have a structure in which a mechanism for flowing a Perfumes or the like is provided in the device, so that the content of the notification matches the fragrance of the perfume, to deliver a perfume that matches the content of the message. by the way For example, a micropump or the like is best as a mechanism for exude a perfume or the like.

• (8) In den obengenannten Ausführungsformen ist als ein Beispiel für das Pulswellendetektionmittel der Pulswellendetektionsabschnitt 10 beschrieben. Die vorliegende Erfindung ist nicht auf den Pulswellendetektionsabschnitt 10 beschränkt und es kann jeder Abschnitt verwendet werden, insofern er die Pulsation erfassen kann.

Of course, these display means may be used either singly or in combination of means.

• (8) In the above embodiments, as an example of the pulse wave detection means, the pulse wave detection section is 10 described. The present invention is not limited to the pulse wave detecting section 10 limited and any section can be used insofar as it can detect the pulsation.

For example, those using transmitted light may be applied although the pulse wave detecting section 10 reflected light used. Incidentally, light having a wavelength range of less than 700 nm tends to be hard to pass through a finger tissue. When transmitted light is used, light having a wavelength in the range of 600 nm to 1000 nm is emitted from an emission portion and passes through tissue, a blood vessel, and tissue in this order to detect a change in the amount of transmitted light. Since the transmitted light in the hemoglobin is absorbed in the blood, the pulse waveform can be detected by detecting the change in the amount of the transmitted light.

In In this case, preferably in the emission section, a laser emitting diode of InGaAs type (indium / gallium / arsenic) or GaAs type (gallium / arsenic) used. The extraneous light with wavelengths in the range of 600 nm to 1000 nm tends to pass through tissue and thus is the S / N ratio of Pulse signals impaired, when the extraneous light is introduced into a light receiving section becomes. Thus, a method can be used in which polarized Laser light emitted from an emission section and the transmitted Light from a light receiving section through a polarizing filter is recorded. this makes possible the detection of pulse signals, free from the effect of extraneous light are at a high S / N ratio.

In this case, as in 61 is shown, an emission section 146 on the side of a fastener 145 arranged, and a light receiving section 147 is located on the side of the body of a wristwatch. The light coming from the emission section 146 is broadcast, passes through a blood vessel 143 , then goes through an area between spoke 148 and elbows 142 and reaches the light receiving section 147 , When the transmitted light is used, it is necessary that the emitted light pass through tissue, and thus its wavelength is preferably in a range between 600 nm and 1000 nm, taking into account the absorption of the tissue.

• (9) In der neunten Ausführungsform wird die Körperbewegungswellenform TH durch den Körperbewegungsdetektionsabschnitt 20 erfasst, und die Pulswellenanalysedaten MKDf werden mit den Körperbewegungsanalysedaten TKDf verglichen, um eine Körperbewegungskomponente zu eliminieren und dadurch die Autokorrelationsdaten RD zu berechnen, auf deren Basis der Pulszustand bestimmt wird. Die Körperbewegungskomponente neigt jedoch dazu, in einer Frequenzzone zu erscheinen, die niedriger als die Frequenz der Grundwelle der Pulswellenform MH ist. Wenn daher eine Frequenzzone, die höher als die Frequenzzone der Grundwelle der Pulswellenform MH ist, als Frequenzzone von Interesse gewählt wird, können der Körperbewegungsdetektionsabschnitt 20, der Wellenformbehandlungsabschnitt 21, der Beurteilungsabschnitt 22, der zweite Wavelet-Transformationsabschnitt 45 und der Körperbewegungskomponenteneliminierungsabschnitt 240 fehlen. Insbesondere, wenn in der Vorrichtung zur Pulswellenuntersuchung 1, wie in 34 dargestellt, eine Frequenzzone, die höher als die die Frequenzzone der Grundwelle der Pulswellenform MH ist, als Frequenzzone von Interesse gewählt wird, kann ein exakter Pulszustand bestimmt werden, selbst wenn eine Körperbewegung vorhanden ist.
• (10) Die zehnte und elfte Ausführungsform zeigen Beispiele, in welchen ein Blutdruckmonitor und ein Pulswellenformmonitor als voneinander getrennte Vorrichtungen gebildet sind. Es kann jedoch eine Struktur angewendet werden, in der der Blutdruckmonitor, der in der zehnten Ausführungsform dargestellt ist, den Pulswellenformmonitor enthält, der in der elften Ausführungsform dargestellt ist.
• (11) Die elfte Ausführungsform zeigt einen Fall, in dem der Berechnungsabschnitt der dikroten Wellenhöhe 544, der Berechnungsabschnitt des dikroten Druckdifferenzverhältnisses 548, der Berechnungsabschnitt des mittleren Blutdruck-Pulsdruck-Verhältnisses und der Berechnungsabschnitt des diastolischen Effusionsdrucks in dem Pulswellenformmonitor bereitgestellt sind. Es kann jedoch mindestens einer dieser Berechnungsabschnitte bereitgestellt sein.

62 Fig. 10 shows a case where an earlobe is used as the detection position. A clamping element 190 and a clamping element 191 be by a spring 192 can be activated and around the center of an axis 193 rotate. The clamping elements 190 and 191 are with a light emission section 194 and a light receiving section 195 provided. When this pulse wave detecting section is used, an earlobe becomes with the clamping elements 190 and 191 clamped to detect a pulse wave.

• (9) In the ninth embodiment, the body movement waveform TH is detected by the body movement detection section 20 and the pulse wave analysis data MKDf are compared with the body movement analysis data TKDf to eliminate a body movement component and thereby calculate the autocorrelation data RD on the basis of which the pulse state is determined. However, the body movement component tends to appear in a frequency zone lower than the frequency of the fundamental wave of the pulse waveform MH. Therefore, if a frequency zone higher than the frequency zone of the fundamental wave of the pulse waveform MH is selected as the frequency zone of interest, the body movement detecting section may 20 , the waveform treatment section 21 , the judging section 22 , the second wavelet transform section 45 and the body movement component eliminating section 240 absence. In particular, when in the device for pulse wave examination 1 , as in 34 As shown, as a frequency zone higher than the frequency zone of the fundamental wave of the pulse waveform MH is selected as the frequency zone of interest, an accurate pulse state can be determined even if body motion is present.
• (10) The tenth and eleventh embodiments show examples in which a blood pressure monitor and a pulse waveform monitor are formed as separate devices. However, a structure may be adopted in which the blood pressure monitor illustrated in the tenth embodiment includes the pulse waveform monitor shown in the eleventh embodiment.
• (11) The eleventh embodiment shows a case where the dicrotic wave height calculating section 544 , the calculation section of the dicrotic pressure difference ratio 548 , the average blood pressure-pulse pressure ratio calculating section and the diastolic effusion pressure calculating section are provided in the pulse waveform monitor. However, at least one of these calculation sections may be provided.

Claims (19)

A pulse wave examination apparatus comprising: a pulse wave detection means ( 10 ) for detecting a pulse waveform (MH) from the detection position of a living body; an autocorrelation calculation means ( 210 ) for calculating autocorrelation data (RD) indicating the autocorrelation of the pulse waveform (MH) generated by the pulse wave detection means (R) ( 10 ) is detected; and a pulse state data acquisition means ( 220 ) for obtaining pulse state data ( 2D ) indicating the type of the pulse waveform on the basis of the autocorrelation data (RD); and wherein the pulse state data extracting means (16) 220 ) generates the pulse state data ZD) by comparing the autocorrelation data (RD) with a prescribed threshold value. A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) a minimum value detection section ( 221 ) for detecting the minimum value of the autocorrelation data (RD) during a period of a heartbeat, and a comparison section ( 222 ) to the Comparing the Minimum Value Obtained from the Minimum Value Detecting Section (FIG. 221 ) is detected with the threshold value to obtain the pulse state data (ZD). A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) a minimum value detection section ( 221 ) for detecting an average minimum value by averaging each minimum value of the autocorrelation data (RD) detected in each of the plurality of heartbeat periods, and a comparison portion (Fig. 222 ) for comparing the average minimum value obtained from the minimum value detecting section (14) 221 ) is detected with the threshold value to obtain the pulse state data (ZD). A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) comprises: a time measuring section ( 223 ) for comparing the autocorrelation data (RD) with the threshold value to measure a time interval in which the autocorrelation data (RD) exceeds or falls below the threshold value; a calculation section ( 224 ) for calculating the ratio of the time interval generated by the time measuring section ( 223 ) is measured, with one period of a heartbeat; and a comparison section ( 225 ) for comparing the result obtained by the calculating section ( 224 ) is calculated with a prescribed threshold to obtain the pulse state data (ZD). A pulse wave examination apparatus according to claim 4, wherein said calculating section (16) 224 ) the ratio of the time interval generated by the time measuring section ( 223 ) is calculated to a period of a heartbeat and the average of the calculated results is calculated. A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) a change rate calculation section ( 224 ) for detecting the rate of change of the autocorrelation data (RD) on the basis of the autocorrelation data (RD), and a change rate comparing portion (RD) 225 ) for comparing the rate of change performed by the rate of change calculation section (16) 224 ) is detected with the threshold value to obtain the pulse state data (ZD). A pulse wave examination apparatus according to claim 6, wherein said change rate comparison section (14) 225 ) detects a maximum value of the rate of change and compares the maximum value of the rate of change with the threshold value to obtain the pulse state data (ZD). A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) comprises: a minimum value detection section ( 221 ) for detecting the minimum value of the autocorrelation data (RD) during a period of a heartbeat; a first comparison section ( 222 ) for comparing the minimum value obtained from the minimum value detecting section (16) 221 ) is detected, with a prescribed first threshold value, to obtain pulse state data (ZD) indicative of a Xuan mai when the minimum value is less than the first threshold value; a time measuring section for comparing the autocorrelation data (RD) with a prescribed second threshold value to measure a time interval in which the autocorrelation data exceeds or falls below the threshold value; a calculation section ( 227 ) for calculating the ratio of the time interval measured by the time measuring section with a period of a heartbeat; and a second comparison section ( 225 ) for comparing the result calculated by the calculating section with a prescribed third threshold to obtain the pulse state data indicative of a ping may or a hua mai. A pulse wave examination apparatus according to claim 1, wherein said pulse state data extracting means (14) 220 ) comprises: a minimum value detection section ( 221 ) for detecting the minimum value of the autocorrelation data (RD) during a period of a heartbeat; a first comparison section ( 222 ) for comparing the minimum value obtained from the minimum value detecting section (16) 221 ) is detected at a prescribed first threshold value to obtain pulse state data (ZD1) indicative of Xuan may if the minimum value is less than the first threshold value; a variation calculation section ( 227 ) for detecting a rate of change (RDd) of the autocorrelation data (RD) based on the autocorrelation data (RD); and a second comparison section ( 225 ) for comparing the rate of change (RDd) received from the rate of change calculation section (RDd) 227 ) is calculated, with a prescribed second threshold, to obtain the pulse state data (ZD2, ZD3) indicative of a ping may or a hua mai. A pulse wave examination apparatus according to claim 8 or 9, wherein the autocorrelation data (RD) is a coefficient of autocorrelation, and the first threshold value used in the comparison operation included in the first comparison section (RD). 222 ) is about 0.25. Apparatus for pulse wave examination according to claim 8, where the autocorrelation data (RD) is a coefficient of autocorrelation are, and the second threshold, in the comparison operation used in the time measuring section is designed so that it is in a range between 0.4 and 0.8. A pulse wave examination apparatus according to any one of claims 1 to 11, further comprising: a body movement detection means (15); 20 ) for detecting the waveform of body movement (TH) indicating the body movement of the living body; and a body movement component eliminating agent ( 30 ) for eliminating a body movement component (MHt) from the pulse waveform (MH) to obtain a body motion-eliminated pulse waveform (MHj), the body movement component (MHt) in the pulse waveform being generated on the basis of the body movement waveform (TH); the autocorrelation computation means ( 210 ) Calculates autocorrelation data (RD) indicating the autocorrelation on the basis of the body motion-eliminated pulse waveform (MHj) instead of the pulse waveform (MH). A pulse wave examination apparatus according to claim 12, further comprising a judging means (16). 22 ) for judging the presence of body motion of the living body based on the body movement waveform (TH) detected by the body movement detecting means (3). 20 ), wherein the body movement component elimination means ( 30 ) stops the body movement eliminating process when the judging means ( 22 ) indicates the absence of body motion to output the pulse waveform (MH) instead of the body motion-eliminated pulse waveform (MHj). A pulse wave analysis apparatus according to any one of claims 1 to 11, further comprising: a first wavelet transformant ( 243 ) for performing a wavelet transformation of the pulse wave form (MH), which of the pulse wave detection means ( 10 ) is detected to obtain pulse wave analysis data (MKD) for each frequency zone; a body movement detection means ( 20 ) for detecting the movement of the living body to output the waveform of the body movement (TH); a second wavelet transformant ( 245 ) for performing a wavelet transformation of the waveform of the body movement (TH) detected by the body movement detection means (FIG. 20 ) is acquired to obtain body movement analysis data (TKD) for each frequency zone; a body movement component eliminating agent ( 240 ) for subtracting the body movement analysis data (TKD) from the pulse wave analysis data (MKD) to obtain body movement-eliminated pulse wave analysis data (MKDaj); and an inverse wavelet transformant ( 247 ) for performing an inverse wavelet transform of the body motion-eliminated pulse wave analysis data (MKDaj) to obtain a body motion-eliminated pulse waveform (MHj); the autocorrelation computation means ( 210 ) Autocorrelation data (RD) indicating autocorrelation is calculated on the basis of the body motion-eliminated pulse waveform (MHj) instead of the pulse waveform (MH). A pulse wave examination apparatus according to any one of claims 1 to 11, further comprising: a wavelet transforming means ( 243 ) for performing a wavelet transformation of the pulse waveform (MH) generated by the pulse wave detection means ( 10 ) is detected to obtain pulse wave analysis data (MKD) for each frequency zone; a body movement component eliminating agent ( 240 ) for eliminating a prescribed frequency component corresponding to a body movement from the pulse wave analysis data (MKD) to obtain body movement-eliminated pulse wave analysis data (MKDaj); and an inverse wavelet transformant ( 247 ) for performing an inverse wavelet transformation of the body motion-eliminated pulse wave analysis data (MKDaj) to a body motion-eliminated pulse waveform (MHj) to win; the autocorrelation computation means ( 210 ) Autocorrelation data (RD) indicating autocorrelation is calculated on the basis of the body motion-eliminated pulse waveform (MHj) instead of the pulse waveform (MH). A pulse wave examination apparatus according to claim 1, further comprising: a first wavelet transforming means (10); 243 ) for performing a wavelet transformation of the pulse waveform (MH) generated by the pulse wave detection means ( 10 ) is detected to obtain pulse wave analysis data (MKD) for each frequency zone; and wherein the autocorrelation computation means ( 210 ) indicates an autocorrelation of the pulse wave analysis data (MKD) in a particular frequency zone. The pulse wave examination apparatus according to claim 16, further comprising: a body movement detection means ( 20 ) for detecting the movement of the living body to output the waveform of the body movement (TH); a second wavelet transformant ( 245 ) for performing a wavelet transformation of the waveform of the body movement (TH) detected by the body movement detection means (FIG. 20 ) is acquired to obtain body movement analysis data (TKD) for each frequency zone; a body movement component eliminating agent ( 240 ) for subtracting the body movement analysis data (TKD) from the pulse wave analysis data (MKD) to obtain body movement-eliminated pulse wave analysis data (MKDaj); and wherein the autocorrelation computation means ( 210 ) indicates an autocorrelation of body motion-eliminated pulse wave analysis data (MKDaj) in a particular frequency zone. The pulse wave examination apparatus according to claim 16, further comprising: a body movement component eliminating means (14); 240 ) for eliminating a prescribed frequency component corresponding to a body movement to obtain body movement-eliminated pulse wave analysis data (MKDaj); and wherein the autocorrelation computation means ( 210 ) indicates an autocorrelation of body motion-eliminated pulse wave analysis data (MKDaj) in a particular frequency zone. Pulse wave examination device according to one of claims 1 to 18, further comprising notification means ( 230 ) for transmitting the pulse state data (ZD) generated by the pulse state data extraction means (ZD) 220 ) be won.