JP3057266B2 - Blood viscosity observation device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a blood viscosity observation device for non-invasively observing the blood viscosity of an artery of a subject by observing the waveform of an arterial pulse wave.

[0002]

2. Description of the Related Art Conventionally, an electrocardiogram, an ultrasonic diagnostic apparatus, and the like have been used for examination of a heart disease. In addition, since arterial pulse waves related to the movement of the heart contain important information indicating the state of blood circulation function, they are widely used for determining the quality of blood circulation function, and generally include the blood content of the capillary. Is observed. This arterial pulse wave is detected by converting the pressure change due to the heartbeat into an electrical signal using a piezo element or condenser microphone, or by detecting the change in blood flow using the modulation effect of hemoglobin in the blood. Is optically detected.

In Oriental medicine, the pathology of an examinee is judged based on the pulse of a tactile sensation, that is, the pulse of the artery at the radius-like protuberance located inside the wrist. In the pulse diagnosis in Oriental medicine, a method is adopted in which the pulse of the above-mentioned mouth is divided into three parts of upper, middle, and lower, that is, three dimensions, seki, seki, and shaku. The dimension refers to the distal side of the artery of the wrist, and a pulse of this dimension represents a person's health from head to chest. In addition, the seki refers to an intermediate point between the peripheral side of the artery and the heart side, and the vein of the seki represents a state of health from the chest to the navel. Furthermore, the scale points to the heart side of the artery and represents the state of health from the navel to the toes.

Conventionally, as a device for obtaining a pulse wave of an artery from an artery of a human body with an infrared sensor, a pressure sensor, or the like, and performing a pulse diagnosis by observing a waveform, for example, a pulse diagnosis disclosed in Japanese Patent Publication No. 57-52054 is disclosed. Devices are known.

As shown in FIG. 9, this pulse diagnostic apparatus includes three pressure sensors 51, 52, and 5 for converting arterial pulse waves at three locations, ie, a size, a size, and a size, into electric signal waveforms.
3 and a patch band 55 for attaching these pressure sensors 51, 52, 53 to the wrist 54 of the examinee and pressing it against the artery. Each of the pressure sensors 51, 52, 53 is
Each of them is arranged side by side on the wrist 54 of the examinee, that is, on a small artery, and the above-mentioned wrapping belt 55 is wound and mounted thereon. Then, compressed air is sent from an air pump through a conduit 56 to an air bag (not shown) provided in the above-mentioned wrapping belt 55, and by adjusting the amount of air, the pressure applied to the artery is varied to change the arterial pulse wave. Change can be measured.

The pressure sensors 51, 52, 53
Is composed of, for example, an electrostatic microphone or a piezoelectric microphone. Specifically, for example, a high DC voltage is applied between the diaphragm electrode and the fixed electrode of the electrostatic microphone via a resistance of several tens of MΩ, and the diaphragm electrode is directly contacted with the small mouth artery, which is a pressure detection point. Then, the pressure changes the distance between the diaphragm electrode and the fixed electrode to change the capacitance, and the voltage generated at this time is detected. The pressure sensors 51, 52, and 53 are connected to electromagnetic oscillographs (not shown) via connection cords 51a, 52a, and 53a, respectively, and record measured arterial pulse waves on recording paper or the like to observe waveforms. I can do it.

[0007]

Conventionally, as described above, an electrocardiogram, an ultrasonic diagnostic apparatus, and the like have been used for examining a heart disease, but an artery that changes with a visceral disease such as a heart disease or a liver disease. There is no means for non-invasive measurement of blood viscosity in the blood, and information on blood viscosity cannot be used for determining visceral disease.

Accordingly, the present invention has been proposed in view of such circumstances, and aims at making it possible to use information of blood viscosity for determination of visceral diseases, and requiring skill. It is intended to provide a blood viscosity observation device capable of non-invasively and accurately determining the viscosity of blood in an artery of a subject.

[0009]

In order to achieve the above-mentioned object, a blood viscosity observation device according to the present invention detects an arterial pulse wave on a heart side by being pressed by a pressing means on a portion to be detected along an artery. A first pressure sensor, a second pressure sensor for detecting a peripheral arterial pulse wave, and a first level detection for detecting that a detection output signal of a predetermined level or more is obtained by the first pressure sensor. Means, second level detecting means for detecting that a detection output signal of a predetermined level or more is obtained by the second pressure sensor, and blood flow passing by which a detection output signal by the second level detecting means is obtained. In the limit state, the measurement is started by the pressure control means for controlling the pressing force by the pressing means and the detection output signal by the first level detection means, and the measurement is started by the detection output signal by the second level detection means. Timer means for terminating, and output means for outputting measurement data from the timer means as blood viscosity measurement data, wherein the first level in the blood flow passage limit state where a detection output signal from the second level detection means is obtained. The present invention is characterized in that blood viscosity observation data quantified as a time difference between a detection output signal from the pressure sensor and a detection output signal from the second pressure sensor is obtained.

[0010]

In the blood viscosity observation apparatus according to the present invention, the first and second pressure sensors are pressed by the pressing means to press the artery, and the predetermined pressure is detected by the second pressure sensor for detecting the pulse wave on the peripheral side. In a blood flow passage limit state where a level detection output signal is obtained, the pressing force of the pressing means is controlled by the pressing control means. Then, in the blood flow passage limit state, the first pressure sensor detects the arterial pulse wave on the heart side, and the second pressure sensor detects the arterial pulse wave on the peripheral side. Obtained as measurement data.

[0011]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the blood circulation function observing apparatus according to the present invention will be described below in detail with reference to the drawings.

The blood circulation function monitoring apparatus according to the present invention is configured as shown in FIG. 1, for example. The blood circulatory function observation device shown in FIG. 1 is used in Oriental medicine.
The present invention is applied to a pulse diagnosis device that detects a pulse wave of a shaku to judge a medical condition of a subject to be examined. First to third pressure sensors ₁ , ₂ , _3, and ₃ and supply the output signals S1, S2, S3 detected by the pressure sensors ₁ , ₂ , ₃ to an output device 4 for observing the waveform. It has become.

The first to third pressure sensors 1, 2, 3
Is composed of, for example, a pressure-electric conversion element such as a piezoelectric microphone, and detects the arterial pulse wave of the above-mentioned size, seki, and scale as a pressure change. As shown in FIG. 2, the first to third pressure sensors 1, 2, and 3 are disposed on the inner wall of a fixed plate 6 connected at both ends by a wrapper 5 attached to the wrist of the examinee. Have been. The first to third pressure sensors 1, 2, and 3 are configured so that the air is injected into the air bag 7 provided in the wrapping band 5, whereby the size, seki, and shaku in the aforementioned Oriental medicine are measured. And the artery 21 is closed via the skin tissue 20 on the wrist of the examinee as shown in FIG.

Air is supplied to the air bag 7 provided on the wrapping band 5 by an air pump (not shown) controlled by a pressing control unit 8, and an exhaust valve (not shown) controlled by the pressing control unit 8. It is supposed to be exhausted through. Further, the first to third air bags 7 are used.
The pressing force of the pressure sensors 1, 2, 3 is applied to the fourth pressure sensor 9
To detect.

Then, the first pressure sensor 1 for detecting the short pulse, that is, the arterial pulse wave on the heart side, supplies the detection output signal S ₁ to the output device 4 and the first level detection circuit 10. And the notch detection circuit 11.

The first level detection circuit 10 detects that the first pressure sensor ₁ has obtained a detection output signal S1 of a predetermined level or more. The detection output signal from the first level detection circuit 10 is supplied to the first and third timer circuits 12 and 15 as a timer start signal.

Further, the first notch detection circuit 11
The detection output signal S _{1 from} the first pressure sensor 1, that is, the notch portion (waveform missing portion) included in the arterial pulse wave on the heart side is detected. The first notch detection circuit 11 includes a low-pass filter 11A that extracts a fundamental wave component of the output signal S1 detected by the first pressure sensor 1, and a _first- pass filter 11A that extracts the fundamental wave component extracted by the low-pass filter 11A. consisting of a subtracter 11B for subtracting from the detection output signals S ₁ by the pressure sensor 1. The first notch detection signal obtained as a subtraction output signal from the subtractor 11B is supplied to the first timer circuit 12 as a timer stop signal and supplied to the integration circuit 14, and further to the second timer circuit 12.
As a timer start signal.

[0018] Then, the first timer circuit 12, the first said that a predetermined level or more detection output signal S ₁ is obtained by the pressure sensor 1 of the first level detection circuit 1
The time from the detection at 0 to the detection of the notch portion included in the detection output signal S ₁ of the first pressure sensor 1 by the first notch detection circuit 11 is measured. The output signal measured by the first timer circuit 12 is
Supplied to Further, the integration circuit 14 integrates the first notch detection signal obtained by the first notch detection circuit 11. The integration output signal from the integration circuit 14 is supplied to the output device 4.

Further, a second pressure sensor 2 for detecting an arterial pulse wave between the heart side and the peripheral side, ie, between the heart side and the peripheral side.
Supplies the detected output signal S ₂ to the output device 4 and to the second level detection circuit 16 and the notch detection circuit 17.

The second level detection circuit 16 detects that the second pressure sensor ₂ has obtained a detection output signal S2 of a predetermined level or more. The output signal detected by the second level detection circuit 16 is supplied to the output device 4 and the pressing control unit 8 and is also supplied to the third timer circuit 15 as a timer stop signal.
It is supplied to the first latch circuit 18 as a first latch signal.

The third timer circuit 15 detects the output signal S ₁ of a predetermined level or more by the first pressure sensor _1.
Since the detection by the first level detection circuit 10 of that is obtained, the second of said second level detection circuit that detects the output signal S ₂ equal to or higher than the predetermined level by the pressure sensor 2 is obtained The time until detection at 16 is measured. The output signal measured by the third timer circuit 15 is supplied to the output device 4.

Further, the second notch detection circuit 17
The detection output signal S2 from the _second pressure sensor 2, that is, a notch portion (waveform missing portion) included in an arterial pulse wave between the heart side and the peripheral side is detected. The second notch detecting circuit 17, a low-pass filter 17 for extracting a fundamental wave component of the detection output signal S ₂ according to the second pressure sensor 2
And A, comprising a fundamental wave component extracted by the low-pass filter 17A and a subtracter 17B for subtracting from the detection output signal S ₂ by the pressure sensor 2 of the second. The second notch detection signal obtained as a subtraction output signal from the subtractor 17B is supplied to the second timer circuit 13 as a timer stop signal.

Then, the second timer circuit 13 detects the notch portion included in the detection output signal S ₁ of the first pressure sensor 1 with the first notch detection circuit 11, a notch portion included in the detection output signal S ₂ of the pressure sensor 2 for measuring the time until the detection by the second notch detecting circuit 17. This second timer circuit 13
Is supplied to the output device 4.

Further, the third pressure sensor 3 for detecting the shortest dimension, that is, the arterial pulse wave on the peripheral side, supplies the detection output signal S ₃ to the output device 4 and the third level detection circuit 19. To supply.

The third level detection circuit 19 detects that the third pressure sensor ₃ has obtained a detection output signal S ₃ of a predetermined level or more. The output signal detected by the third level detection circuit 19 is supplied to the second latch circuit 20
Is supplied as a second latch signal.

Further, the first air bag 7
To the fourth pressure sensor 9 for detecting the pressing force of the third pressure sensor 1, 2, 3, and supplies the detection output signal S ₄ to the first and second latch circuits 18 and 20.

The first latch circuit 18 outputs the detection output signal S ₄ from the fourth pressure sensor 9 to the first latch signal, that is, the second level detection circuit 16.
, And the latched output signal is supplied to a subtractor 21 and a divider 22. The latch output signal from the first latch circuit 18 is such that the blood flow is completely passed below the first pressure sensor 1 and a detection output signal S ₂ of a predetermined level or more is obtained by the second pressure sensor 2. shows the blood flow full passage pressure P ₁ to be.

Further, the second latch circuit 20 latches the output signal S ₄ detected by the fourth pressure sensor 9 by the second latch signal, that is, the output signal detected by the third level detection circuit 19, The latch output signal is supplied to the subtractor 21. This second latch circuit 2
0 latch output signal by, the second the third pressure sensor 2 below is blood flow and all-pass state of the predetermined level or more detection output signal S ₄ is obtained blood allpass pressure by the pressure sensor 3 shows the P _2.

The subtracter 21 outputs the second latch circuit 2 from the latch output signal of the first latch circuit 18.
The latch output signal by 0 is subtracted, and the subtracted output signal is supplied to the divider 22. The subtraction output signal from the subtracter 21 is obtained by combining the blood flow total passage pressure P _1, which is indicated by the latch output signal of the first latch circuit 18 with the blood flow under the first pressure sensor 1, with the blood flow in the whole state. The pressure difference P ₁ -P ₂ from the blood flow total passage pressure P _{2 at} which the blood flow is completely passed below the second pressure sensor 2 is indicated by the latch output signal of the second latch circuit 20.

The divider 22 is connected to the subtractor 2
The pressure difference P ₁ -P ₂ indicated by the subtraction output signal is normalized by dividing the subtraction output signal by 1 by the latch output signal by the first latch circuit 18. The divided force signal by the divider 22, that is, the normalized pressure difference information (P ₁ −P ₂ ) / P ₁ is supplied to the output device 4.

The pulse diagnostic apparatus having such a configuration is used by switching its operation state to the first to third operation modes.

First, in the first operation mode, an air pump and an exhaust valve (not shown) are controlled by the pressing control section 8 to control the first to third pressure sensors 1, 2, 3 by the air bag 7. The pressing force is gradually changed from the blood flow blocking state to the full passage state, and the output signals S ₁ , S ₂ , S ₃ of the first to third pressure sensors ₁ , ₂ , ₃ are output by the output device 4. Observe. Thus, it is possible to determine the medical condition of the examinee by observing the arterial pulse wave at the size of the mouth, the seki and the shaku in Oriental medicine.

Here, the detection output signals S ₁ , S ₂ , S ₃ of the first to third pressure sensors 1, ₂ , ₃ are converted to the first to third pressure sensors 1 by the air bladder 7. , 2,
In the case where the pressing force of No. 3 is gradually changed from the blood flow blocking state to the full passage state, as shown in FIG. 4, _first , the signal level of the detection output signal S1 from the _first pressure sensor 1 located on the heart side is changed. A second pressure sensor 2 which rises and then is centrally located
The signal level of the detection output signal S ₂ rises due to, finally a third signal level of the detection output signal S ₃ by the pressure sensor 3 located on the distal rises, the pressing force is reduced first
In addition, the signal levels of the detection output signals S ₁ , S ₂ , and S _{3 from} the third to third pressure sensors ₁ , ₂ , and ₃ decrease at the same time.

In the second operation mode, the pressing force of the first to third pressure sensors 1, 2, 3 by the air bladder 7 is gradually reduced from the state in which blood flow is interrupted, and the second level is set. Based on the detection output signal from the second level detection circuit 16, the pressing control unit 8 controls the pressing force P _{1 so} as to keep the pressing force P ₁ constant in the blood flow passage limit state where the detection output signal from the detection circuit 16 is obtained. It controls an air pump and an exhaust valve (not shown).

Here, in the above-mentioned blood flow passage limit state, the first
When the waveforms of the detection output signals S ₁ and S ₂ obtained by the second pressure sensors 1 and ₂ are observed by the output device 4, FIG.
The solid line shows the waveform of the detection output signal S ₁ of the first pressure sensor 1 and the broken line shows the waveform of the detection output signal S ₂ of the second pressure sensor 2. When the circulatory function is normal, a mountain-like waveform smoothly continues from the time point t ₁ at which the systole starts to the time point t ₂ at which the aortic valve is closed.

[0036] By contrast, the notch occurs in the middle from the ventricular contraction start time t ₁ to aortic time t ₂ when there is an abnormality in the examinee's blood circulatory function. For example, in the case of a pressure abnormality that is rapidly propagated due to a valve abnormality or the like, the waveform of the detection output signal S1 of the _first pressure sensor 1 is shown by a solid line in FIG. 6, and the detection output signal S1 of the second pressure sensor 2 is shown in FIG. Notches n ₁ and n ₂ appear at approximately the same time t _n as shown by the broken line in waveform ₂ . Further, in the case of a flow abnormality having a slow propagation due to, for example, an abnormality of the myocardium, the waveform of the detection output signal S1 of the _first pressure sensor 1 is shown by a solid line in FIG.
Notches n ₁ and n ₂ with a time difference Δt appear as shown by a broken line in the waveform of the detection output signal S ₂ of the second pressure sensor 2.

In the second operation mode, the pulse diagnosing device sets a time t _n from the start of the ventricular contraction t ₁ to the appearance of the notch n _{1 in} the detection output signal S ₁ of the first pressure sensor 1. as well as measured by the first timer circuit 12, the notch n ₂ appears in the detection output signal S ₂ of the second pressure sensor 2 from the notch n ₁ to the first detection output signal of the pressure sensor 1 appears The time up to, that is, the time difference Δt between the notches n ₁ and n ₂ is measured by the second timer circuit 13, and the occurrence time information t _n and Δt of each notch n ₁ and n ₂ are displayed on the output device 4.

As described above, skill is required by displaying the respective measurement data t _n and Δt by the first and second timer circuits 12 and 13 as blood circulation function observation data on the output device 4. In addition, the state of the blood circulation function of the examinee can be determined non-invasively and accurately.

Further, the first notch detection signal by the first notch detection circuit 11 for detecting the notch n ₁ appearing in the detection output signal S ₁ of the first pressure sensor 1 is integrated by the integration circuit 14. By calculating the size (area) of the notch n, the state of the disease can be quantified. By displaying the integrated output signal of the integration circuit 14 as blood circulation function observation data on the output device 4, the disease can be obtained. Can be more accurately determined.

In the second operation mode, the third timer circuit 15 determines that the detection output signal S ₁ of a predetermined level or more is obtained by the first pressure sensor 1. from the detection by the detection circuit 10, the second said that the detection output signal S ₂ higher than a predetermined level is obtained by the pressure sensor 2 of the second level detection circuit 16
, Ie, the time τ required for blood to move by the distance L between the first pressure sensor 1 and the second pressure sensor 2 is measured.

Here, in the above-mentioned blood flow passage limit state, the first
Velocity V at which blood moves using the pressure sensor 1
Is, as shown in Equation 1,

(Equation 1)

Since the blood viscosity μ depends on the blood viscosity μ, the blood viscosity μ is measured by measuring the time τ required for blood to move by the distance L between the first pressure sensor 1 and the second pressure sensor 2. Can be estimated.

The output device 4 to which the output signal of the third timer circuit 15 is supplied moves blood by a distance L between the first pressure sensor 1 and the second pressure sensor 2. Is displayed as measurement data of the blood viscosity μ. This makes it possible to obtain blood viscosity information in which the blood viscosity μ of the artery is normalized non-invasively.

[0044] Further, in the second mode of operation, the comparison output of the detection output signal S ₂ according to the first reference waveform signal and the second pressure sensor 2 based on the detection output signals S ₁ by the pressure sensor 1 of The signal is displayed as a waveform by the output device 4 as the blood vessel inner wall state observation information. The blood moving as a thin film flow under the first pressure sensor 1 in the blood flow passage limit state presents a wavefront (indicating an increase or decrease in pressure) according to the rough state of the inner wall of the blood vessel of the artery. 2 pressure sensors 2
Detection output signal S ₂ by, as shown in FIG. 8, a waveform corresponding to rough state of the inner vessel wall of the artery. Therefore, it is possible to obtain the roughness information of the inner wall of the blood vessel of the artery in a non-invasive manner.

In the second operation mode, the waveforms of the detection output signals S ₁ and S ₂ by the first pressure sensor 1 on the heart side and the second pressure sensor 2 at the center are observed. By having the third pressure sensor 3 on the peripheral side,
High-accuracy waveform observation can be performed by removing the influence of peripheral blood.

Next, in the third operation mode, the pressing force of the first to third pressure sensors 1, 2, 3 by the air bag 7 is gradually reduced from the blood flow cutoff state. The control unit 8 controls an air pump and an exhaust valve (not shown), and uses the normalized pressure difference information (P ₁ −P ₂ ) / P ₁ indicated by the division calculation force signal by the divider 22 as the arterial hardness observation information. It is displayed on the output device 4.

Here, the first to third pressure sensors 1 and 2 arranged adjacent to each other along the artery as in this pulse diagnosis device
When the pressures 2 and 3 are pressed, the load by the first pressure sensor 1 on the heart side and the third pressure sensor 3 on the peripheral side affects the center where the second pressure sensor 2 is located, and the center load increases. . The increase in the load has a positive correlation with the hardness of the artery of the wrist of the examinee who presses the first to third pressure sensors 1, 2, and 3. Therefore, the whole blood flow passing pressure P _{1 at} which the blood flow passes under the first pressure sensor 1 on the heart side, and the blood flow passes under the second pressure sensor 2 at the center. Pressure difference P _{1 from} total blood flow passage pressure P ₂
-P ₂ can be used as information indicating the hardness of the artery of the wrist of the examinee. The pressure difference P ₁ -P ₂ is hardly affected by the blood pressure and the individual difference of the skin tissue, because the blood flow total passage pressure point is the balance point between the systolic blood pressure and the load via the skin tissue.

In the present embodiment, the pressure difference P ₁ -P ₂ is normalized by the divider 22 and displayed on the output device 4 as arterial stiffness observation information in which individual differences due to blood pressure and the like are eliminated. . Thereby, arterial hardness observation information can be obtained non-invasively.

[0049]

As described above, in the blood viscosity observation apparatus according to the present invention, in the blood flow passage limit state where a predetermined level detection output signal is obtained by the second pressure sensor for detecting the peripheral arterial pulse wave. , Detecting the arterial pulse wave on the heart side
Blood viscosity observation data quantified as the time difference between the detection output signal from the pressure sensor of the above and the detection output signal from the second pressure sensor for detecting the peripheral artery pulse wave is obtained and output from the output means, so skill is required. It is possible to accurately determine the blood viscosity of the examinee non-invasively without having to perform the above procedure. Therefore, the information on the blood viscosity can be used for determining the visceral disease.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a configuration of a pulse diagnosis device to which the present invention is applied.

FIG. 2 is a perspective view showing an arrangement state of three pressure sensors used in the pulse diagnostic apparatus shown in FIG.

FIG. 3 is a sectional view showing a state in which an artery is pressed by three pressure sensors in the pulse diagnostic apparatus shown in FIG. 1;

FIG. 4 is a characteristic diagram showing a change state of a signal level of each detection output signal obtained by three pressure sensors in the pulse diagnostic apparatus shown in FIG.

FIG. 5 shows a case where the blood circulation function of the subject is normal.
FIG. 7 is a waveform chart showing waveforms of respective detection output signals obtained by first and second pressure sensors in the pulse diagnostic device shown in FIG.

FIG. 6 is a waveform chart showing an observed waveform of a pressure abnormality of a blood circulation function by the pulse diagnostic apparatus shown in FIG. 1;

FIG. 7 is a waveform chart showing an observed waveform of a flow abnormality of a blood circulation function by the pulse diagnostic apparatus shown in FIG. 1;

FIG. 8 is a waveform chart showing an observation waveform of a state of an inner wall of a blood vessel by the pulse diagnostic apparatus shown in FIG. 1;

FIG. 9 is a perspective view showing a pulse wave detecting device for detecting a pulse wave of a size, a seki and a shaku in Oriental medicine.

[Explanation of symbols]

 Pressure sensor 4 Output device 7 Air bag 9 Press control unit 10, 16 Level detection Circuit 15 Timer circuit

──────────────────────────────────────────────────続 き Continued on the front page (58) Field surveyed (Int.Cl. ⁷ , DB name) A61B 5/02-5/0295 A61B 10/00

Claims (1)

(57) [Claims] A first pressure sensor for detecting an arterial pulse wave on the heart side and a second pressure sensor for detecting an arterial pulse wave on the peripheral side, which are pressed by a pressing means to a detection site along the artery; First level detecting means for detecting that a detection output signal of a predetermined level or more is obtained by the first pressure sensor; and detecting that a detection output signal of a predetermined level or more is obtained by the second pressure sensor. Second level detecting means for detecting, pressing control means for controlling pressing force by the pressing means in a blood flow passage limit state where a detection output signal from the second level detecting means is obtained, and the first level Timer means for starting measurement by a detection output signal from the detection means and ending measurement by the detection output signal from the second level detection means; And output means for outputting as in the first pressure sensor in the blood flow passage limit condition in which the detection output signal is obtained by the second level detection means
Detection output signal and the detection output by the second pressure sensor.
A blood viscosity observation device characterized in that blood viscosity observation data quantified as a time difference from a signal is obtained.