JP4388356B2 - Blood flow velocity measuring device and measuring method - Google Patents

Description

  The present invention relates to a blood flow rate measurement method and a blood flow rate measurement device for diagnosis of blood rheology in a living body.

  As one of the examination items for judging the health condition of the human body, blood rheology measurement focusing on blood fluidity has attracted attention. As a means for measuring blood rheology, an apparatus (product name MC-FAN) for measuring the time required for a certain amount of blood collected from a subject to pass through a microchannel (microchannel) has been developed (see Non-Patent Document 1). ). At present, the MC-FAN apparatus is a standard machine in blood rheology measurement.

  However, in the measurement using the MC-FAN apparatus, blood must be collected as described above, and the measurement can be performed only by medical institutions, which is extremely inconvenient for the purpose of easily checking the health condition of anyone at any time. large. In addition, blood collection has a large physical and psychological burden on the subject, and since the number of times that can be measured per day is only a few times at most, continuous data cannot be obtained in time series.

There is a strong correlation between blood rheology and blood flow velocity in vivo. That is, it is considered that when the viscosity of blood is high, the blood flow velocity is slow, and when the viscosity is low, the blood flow velocity is high. Therefore, it is possible to know blood rheology indirectly by measuring the blood flow velocity in the living body. Therefore, in order to measure the blood flow velocity that has a strong correlation with blood rheology, the invention has been devised to measure the blood flow velocity from the Doppler shift of the ultrasonic wave that propagates in the living body and reflects to the blood flow in the blood vessel. Yes. (See Patent Document 1)
JP 2003-159250 A Keiji Kikuchi “Measurement of whole blood fluidity using a capillary model” (Food Research Result Information, NO.11, 1999)

  However, the conventional technique for measuring the blood flow velocity from the Doppler shift of the ultrasonic wave that propagates in the living body and reflects on the blood flow in the blood vessel has a random motion in the blood flow, and the ultrasonic Doppler measurement Since it is necessary to amplify a minute signal greatly, the influence of an external noise signal is large, and a large noise component is easily included in the output signal, so that a signal having an excellent S / N ratio (signal noise ratio) can be obtained. There is a problem that it is difficult to obtain.

  Therefore, the present invention provides a blood flow velocity measuring apparatus and measurement method that enables anyone other than an expert to easily measure an accurate blood flow velocity and know blood rheology without collecting blood. The purpose is to do.

  In order to solve the above problems, the present invention uses a composite blood flow rate sensor that combines an ultrasonic sensor comprising an ultrasonic transmitter and an ultrasonic receiver and an optical sensor that measures the absorption of light by blood. Measured from the optical Doppler signal using the time (phase) of the peak value of the light absorption waveform obtained from the optical sensor or the time (phase) of the peak value of the differential waveform of the light absorption signal as a reference point. Synchronous addition processing is performed to superimpose the frequency distribution or velocity distribution waveform for each beat of the pulse. This synchronous addition process makes it possible to obtain a blood flow velocity even from a signal with a relatively poor S / N.

  It is possible to measure blood flow velocity that has a strong correlation with blood rheology in a non-invasive manner without collecting blood from the subject, and to remove noise components from signals with inferior S / N obtained from the ultrasonic Doppler measurement method. Blood flow velocity can be measured, so the S / N ratio is improved several times, and more accurate blood flow velocity measurement is possible. But you can easily check the exact rheology and use it to check your health.

(Embodiment 1)
FIG. 1 shows a flowchart of the measurement method according to Embodiment 1 of the present invention, FIG. 2 shows the configuration of the measurement apparatus used in the present invention, and FIG. 3 shows the composite blood flow velocity sensor used in the present invention. FIG. 7 is a schematic diagram showing an outline of the ultrasonic Doppler signal measurement principle, and FIG. 8 is a schematic diagram showing an outline of the optical signal measurement principle.

  The composite blood flow velocity sensor is a combination of ultrasonic sensors 1a and 1b including transmitting elements 2a and 2b and receiving elements 3a and 3b, and an optical sensor 7 including a light emitting element 8 and a light receiving element 9. The transmitting elements 2a and 2b and the receiving elements 3a and 3b of the ultrasonic sensors 1a and 1b are all ultrasonic elements in which an electrode thin film is formed on a piezoelectric ceramic. The frequency of the ultrasonic wave was 15 MHz. The light-emitting element 8 is a high-intensity light-emitting diode whose emission color is blue, and the light-receiving element 9 uses a photodiode or a phototransistor. In the present invention, two pairs of ultrasonic sensors 1a and 1b are used and arranged on the sensor support substrate 10 so that the directions of directivity of ultrasonic emission and reception are not parallel to each other. Further, the optical sensor 7 is disposed at an intermediate position between the ultrasonic sensors 1a and 1b. In this embodiment, two pairs of ultrasonic sensors of the composite blood flow velocity sensor are used. However, the present invention can be carried out by using one pair of ultrasonic sensors or two or more pairs. Is possible.

  After the measurement preparation and initial value setting (S1) are performed on this composite blood flow velocity sensor, the blood flow velocity in the blood vessel 72 is measured by bringing the subject's fingertip (living body) 71 into contact with the sensor as shown in FIG. To do. The 15 MHz ultrasonic wave (transmitted wave 13a) emitted from the transmitting element 2a of the ultrasonic sensor 1a propagates through the living tissue and is reflected by the blood flowing through the blood vessel 72. The reflected wave 14a changes to a signal subjected to Doppler shift according to the blood flow velocity. This reflection is received by the receiving element 3a. Similarly, for the ultrasonic sensor 1b, the ultrasonic wave (transmitted wave 13b) emitted from the transmitting element 2b is reflected by the Doppler shift due to blood flow and detected by the receiving element 3b, but the ultrasonic wave is emitted. Directional direction is different. As shown in FIG. 2, the signals of the reflected waves 14a and 14b received by the receiving elements 3a and 3b are respectively amplified by the preamplifier circuits 22a and 22b, detected by the detector circuits 23a and 23b, and the base ultrasonic waves. Only the Doppler signal component from which the carrier component is removed is extracted, the high-frequency components unnecessary for the A / D conversion processing are removed by the filter circuits 24a and 24b, and again amplified by the post-stage amplifier circuits 25a and 26b, respectively. The data is converted into digital data by the A / D converters 26a and 26b, temporarily stored in the buffer memory 32 (S2), and then transferred to the main memory (S5). Here, in this embodiment, the sampling frequency of the A / D converters 25a and 25b is 20 kHz.

  As described above, the ultrasonic sensor detects the blood flow velocity in the blood vessel 72, while the optical sensor 7 detects the blood volume at a local site in the living body. Part of the incident light 15 emitted from the light emitting element 8 of the optical sensor 7 is absorbed by blood. Therefore, the reflected light 16 received by the light receiving element 9 decreases when the blood volume is large, and conversely, the reflected light 16 received by the light receiving element 9 increases when the blood volume is small. The part of the living body detected by the small optical sensor 7 is local, and the amount of blood existing in the part increases and decreases with the pulse of the subject. Therefore, the optical signal voltage obtained from the light receiving element 9 is the pulse of the subject. The signal increases or decreases with the period. Usually, since a signal proportional to the blood volume is required, the optical signal is used after being converted into a waveform in which positive and negative are reversed. If the signal line of the measurement circuit is connected reversely or cannot be dealt with depending on the circuit configuration, an inversion operation process may be performed after A / D conversion. Of course, the ultrasonic Doppler signal and the optical signal fluctuate synchronously with the pulse of the person being measured. The optical signal thus obtained is also A / D converted, temporarily stored in the buffer memory 32, and transferred to the main memory 37 (S5). In order to measure the blood viscosity (rheology) of the subject, blood flow velocity is measured for several tens of seconds (S3), and data is accumulated.

  In general, for an ultrasonic Doppler signal obtained by an ultrasonic sensor, a high-intensity LED light source and a high-sensitivity photosensor are available recently, so that an optical signal has high sensitivity and excellent S / N data. Therefore, it is easy to detect the waveform peak. Therefore, even when the S / N of the Doppler signal is extremely bad, the phase information (peak time) of the optical signal can be used for noise removal processing of the Doppler signal.

  Peak detection of the optical signal (light absorption amount signal) obtained by the above measurement is performed. Since this optical signal reflects the amount of light absorption, the negative (convex downward) peak of the waveform is the blood volume peak. After removing unnecessary high-frequency components from the optical signal data to form a smooth waveform (S6), the data is smaller in absolute value than the average value of the signal. The order d) of the discrete data string is recorded in the main memory 37, and this time is tp (1) (or data order dp (1)). The time of the next peak data is tp (2), and the nth peak time is tp (n) (S8, S9). n is the number of pulses of the subject during the measurement time at the maximum. FIG. 4 shows an example of an optical signal waveform and its differential waveform. The waveform of the blood flow velocity in FIG. 4 is obtained by plotting values calculated from the Doppler signal, and is a waveform that is not subjected to the synchronous addition processing of the present invention. Therefore, the waveform is over the entire measurement time.

  Each Doppler signal obtained by the above measurement is replaced with frequency distribution data by Fourier transform (FFT) processing (S10). Here, if the number of data in the FFT processing is Nf, the FFT processing is performed on each Nf data from the time point tp (1) or the data order dp (1). This is performed until the next peak time tp (2) or data order dp (2). The n-th peak is performed in a section from tp (n) to tp (n + 1) or dp (n) to dp (n + 1). This is repeated until the last peak of the data. When the sampling frequency of A / D conversion is fs = 20 kHz and the number of FFT processing is Nf = 256, frequency distribution data every 0.0128 seconds can be obtained (however, the number of data of FFT processing and the FFT processing) For example, it is possible to process 256 data at intervals of 0.01 seconds).

Next, synchronous addition processing of frequency distribution data with reference to the peak time tp of the optical signal is performed. The frequency distribution data resulting from FFT processing of Nf data from tp (1) (or dp (1)) is F (1,1), the next data is F (1,2), and the mth data is F. The m-th frequency distribution data of (1, m), tp (n) (or dp (n)) is F (n, m), and the intensity A of the reference frequency component f (0) in the frequency distribution data is Let A (n, m, 0) and the intensity of the frequency component f (i) be A (n, m, i). Of these frequency distribution data, n synchronous additions As (m, i) of m-th frequency f (i) from the peak time tp are:
As (m, i) = A (1, m, i) + A (2, m, i) +,..., + A (n, m, i)
It becomes. This process is performed for each m and i (S11). Although the original frequency distribution data includes random noise components, the addition of the noise components converges to reduce the noise components. FIG. 5 shows an example of the frequency distribution. The horizontal axis represents the frequency component expressed as a multiple of the reference frequency in the FFT processing, and the vertical axis represents the relative intensity. FIG. 5A, FIG. 5B, and FIG. 5C are original data before performing addition processing, and the original data is extracted from 20 data, and only the first, second, and twentieth. Is shown in each. The original data has a large variation in the intensity of frequency components. However, by performing the synchronous addition process 20 times, the S / N ratio is relatively improved several times. FIG. 5 (d) shows that after the addition process, the intensity variation of each frequency component is reduced and the S / N is improved. Since a person's pulse is about several tens to several hundreds of times in 60 seconds, measurement of several tens of seconds or more is required to collect the necessary data amount.

  Note that it is not necessary to perform the above processing on all data obtained from the sensor. Ignoring the data included in the time when the blood flow is low, the data included in the time when the blood flow increased in the pulse period, that is, the peak of the optical signal (light absorption) waveform in the pulse period (T). The processing may be performed for a half time (T / 2). Since the amount of data to be processed can be reduced, the time required for processing of the arithmetic unit (processor) can be shortened.

  Next, the frequency component having the highest frequency is selected from each frequency distribution data obtained by the above method. If the maximum frequency obtained from the data of the ultrasonic sensor 1a is Fa and the maximum frequency obtained from the data of the ultrasonic sensor 1b is Fb, the maximum blood flow velocity V can be derived by the following equation (S12). .

V = cFa / 2Fcosθ
Here, θ = atan ((− cos α−Fb / Fa) / sin α)
α is the angle formed by the directivity of the emission and reception of the ultrasonic waves of the two ultrasonic sensors, c is the speed of sound in the living body, and F is the transmission frequency (drive frequency) of the ultrasonic sensors. If the maximum blood flow velocity V is large, the blood fluidity in the living body is relatively high, and if V is small, the blood fluidity is low.

  In addition, it is possible to perform the same synchronous addition processing on the velocity distribution data derived from the frequency distribution by the Doppler shift principle, and there is no principle difference between the processing with the frequency distribution data and the processing with the velocity distribution data. .

Then, the data of these processing results are stored in the storage 38 (S13) and displayed on the screen, thereby making it possible to know the blood fluidity of the measurement subject (S14).
(Embodiment 2)
FIG. 6 shows a flowchart of the measurement method according to the second embodiment of the present invention.

  In the ultrasonic Doppler signal waveform and optical absorption signal waveform obtained from the blood flow of an actual living body (human body), depending on the measurement position, the peak of the optical absorption signal is at a point slightly behind the peak of the Doppler signal waveform There is. This is considered to be because the blood flow velocity increases when the blood volume at the fingertip increases with the pulse, and the blood flow velocity starts to decrease at the maximum (peak) blood volume. That is, the maximum value of the blood flow velocity is also present near the peak of the increase (increment) of the light absorption signal. Therefore, in the first embodiment, the peak value of the optical signal itself is used. However, in the second embodiment, the Doppler signal waveform is converted by FFT calculation processing with reference to the peak time tΔp of the differential waveform of the optical absorption signal waveform. Synchronous addition processing of the frequency distribution waveform is performed.

  When the differential waveform is used, after the A / D conversion of the optical signal, the digital difference processing may be performed digitally using a digital arithmetic processing device (S7), or the operational amplifier circuit (OP amplifier) ) May be converted into a differential waveform by an analog differential circuit, and then A / D conversion may be performed and taken into an arithmetic processing unit.

  Also in the second embodiment, in order to save the processing time, the Doppler signal is used only for data of a half time (T / 2) including the peak of the differential waveform of the optical signal in the pulse period (T). It is sufficient to perform synchronous addition processing of the frequency distribution waveforms.

  The present invention is not only capable of measuring a blood flow velocity in a living body having a strong correlation with blood rheology as an index indicating fluidity of fluid for the purpose of medical care and health maintenance / promotion. It can also be used in measurement to know the correlation between the activity state of the human body) and the blood flow state in each part of the living body.

Flow chart showing the measurement method of the present invention The block diagram which shows the structure of the measuring device of this invention Compound blood flow velocity sensor used in the present invention An example of each signal waveform by the measuring device of the present invention Example of frequency distribution data Flow chart showing the measurement method of the present invention Schematic diagram showing the outline of ultrasonic Doppler signal measurement principle Schematic diagram showing the outline of optical signal measurement principle

Explanation of symbols

DESCRIPTION OF SYMBOLS 1a, 1b Ultrasonic sensor 2a, 2b Transmitting element 3a, 3b Receiving element 7 Optical sensor 8 Light emitting element 9 Light receiving element 10 Sensor support substrate 13a, 13b Transmitted wave 14a, 14b Reflected wave 15 Incident light 16 Reflected light 21 Transmitting circuit 22a, 22b Preamplifier circuit 23a, 23b Detector circuit 24a, 24b, 28 Filter circuit 25a, 25b Subsequent amplifier circuit 26a, 26b, 29, 31 A / D converter 27 Amplifier circuit 30 Differentiating circuit 32 Buffer memory 33 Processing unit 34 Digital Input unit 35 Signal calculation unit 36 General-purpose calculation unit 37 Main memory 38 Storage 39 Input / output device, etc.

Claims (6)

An ultrasonic sensor that irradiates blood flowing in the blood vessels of a living body with ultrasonic waves and detects the Doppler shift of the reflected wave, and an optical sensor that irradiates light on the living body and detects reflection / absorption of light by blood in the living body And a blood flow velocity measuring method for deriving a blood flow velocity in a living body from a Doppler signal obtained from the ultrasonic sensor and an optical signal obtained from the optical sensor,
A synchronous addition process for performing a synchronous addition process of superimposing a plurality of frequency distribution or velocity distribution waveforms periodically obtained for each pulse from the Doppler signal in synchronization with a phase of a periodic optical signal waveform associated with a pulse of a living body Prepared,
The synchronous addition step is a synchronous addition in which a frequency distribution or a velocity distribution waveform obtained from the Doppler signal is overlapped in synchronization with the phase of the differential waveform of the optical signal on the basis of the phase of the peak value of the differential waveform of the optical signal. A blood flow velocity measuring method characterized by performing processing. As the ultrasonic sensor, two pairs of ultrasonic sensor elements arranged so that the direction in which the ultrasonic wave is emitted and the direction in which the reception sensitivity is directed are not parallel to each other, a Doppler signal obtained from each ultrasonic sensor, and an optical sensor Is a blood flow velocity measurement method that derives the blood flow velocity from the optical signal obtained from
The synchronous addition step performs a synchronous addition process of superimposing the frequency distribution or velocity distribution waveforms obtained from the respective Doppler signals of the ultrasonic sensors in synchronization with the phase of the optical signal waveform, 2. The blood flow velocity measuring method according to claim 1 , wherein the velocity signals are synthesized based on an angle formed by the acoustic wave sensor. The synchronous addition step analyzes only the data of the Doppler signal during a time of half or less of the pulse period including the peak of the optical absorption signal of the optical signal waveform or the peak of the differential waveform. The blood flow velocity measuring method according to any one of 1 to 2 . An ultrasonic sensor that irradiates blood flowing in the blood vessels of a living body with ultrasonic waves and detects the Doppler shift of the reflected wave, and an optical sensor that irradiates light on the living body and detects reflection / absorption of light by blood in the living body A blood flow velocity measuring device for deriving a blood flow velocity in a living body from a Doppler signal obtained from the ultrasonic sensor and an optical signal obtained from the optical sensor,
Detection means for detecting a phase of a periodic optical signal associated with a pulse of a living body, and synchronization for superimposing a frequency distribution or velocity distribution waveform periodically obtained for each pulse from the Doppler signal in synchronization with the phase of the optical signal Addition processing means,
The detection means comprises means for converting the optical signal into its differential waveform, and means for detecting the phase of the peak value of the differential waveform of the converted optical signal,
The synchronous addition processing means superimposes a frequency distribution waveform or a velocity distribution waveform obtained from a Doppler signal in synchronization with a phase of a peak value of a differential waveform of a periodic optical signal accompanying a pulse of a living body. Flow velocity measuring device. The ultrasonic sensor is composed of two pairs of ultrasonic sensor elements arranged at an angle where the ultrasonic wave emission direction and the reception sensitivity directing direction are not parallel to each other,
The synchronous addition processing means performs synchronous addition processing for superimposing the frequency distribution or velocity distribution waveforms obtained from the respective Doppler signals of the ultrasonic sensors in synchronization with the phase of the optical signal waveform, and then two pairs. The blood flow velocity measuring device according to claim 4 , wherein the velocity signals are synthesized based on an angle formed by the ultrasonic sensor element. The synchronous addition processing means analyzes only the data of the Doppler signal during a time that is not more than a half of the pulse period including the peak of the optical absorption signal of the optical signal or the peak of the differential waveform thereof. The blood flow velocity measuring device according to any one of 4 and 5 .

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