JP4807598B2 - Pulse photometer - Google Patents

Description

The present invention relates to signal processing for extracting two common signals extracted from a single medium at the same time to extract a common signal component, and more particularly, a pulse used in the medical field, particularly for diagnosis of the circulatory system. The present invention relates to improvement of signal processing in a photometer.

Various methods have been proposed for separating a signal component and a noise component from two signals extracted almost simultaneously from one medium.
In general, they are processed in the frequency domain or the time domain.
Even in the medical field, a device that measures the pulse waveform and pulse rate, which is called a photoelectric pulse wave meter, a concentration measurement of light-absorbing substances in blood, a device for measuring oxygen saturation SpO2, carbon monoxide hemoglobin, Met hemoglobin, etc. A device for measuring the concentration of special hemoglobin, a device for measuring the concentration of injected dye, and the like are known as pulse photometers.
In particular, the oxygen saturation SpO2 measuring device is called a pulse oximeter.

The principle of the pulse photometer is that pulse wave data obtained by transmitting or reflecting light of multiple wavelengths with different absorption to the target substance to the living tissue and continuously measuring the amount of transmitted or reflected light. The concentration of the target substance is obtained from the signal.
If noise is mixed in the pulse wave data, the correct concentration cannot be calculated, and there is a risk of mishandling.
Conventionally, in a pulse photometer, in order to reduce noise, a method of dividing a frequency band and paying attention to a signal component or taking a correlation between two signals has been proposed.
However, these methods have a problem that analysis takes time.

Therefore, in the patent No. 32701717 (Patent Document 1), the applicant of the present invention irradiates the biological tissue with light of two different wavelengths and expresses the magnitudes of the two pulse wave signals obtained from the transmitted light on the vertical axis, Draw a graph as the horizontal axis, find the regression line, and based on the slope of the regression line,
It has been proposed to determine oxygen saturation or light-absorbing substance concentration in arterial blood.
According to the present invention, measurement accuracy can be improved and power consumption can be reduced.
However, in order to obtain the regression line or its inclination using a large amount of sampling data for pulse wave signals of each wavelength, a lot of calculation processing is still required.

Further, the present applicant uses frequency analysis in Japanese Patent Application No. 2001-332383 (Patent Document 2), but in the analysis, the pulse wave signal itself is not extracted as in the prior art. In order to obtain the fundamental frequency of a wave signal and to further improve the accuracy, a method of filtering the pulse wave signal using a filter using the harmonic frequency is proposed.
However, further improvements have been desired in terms of obtaining the fundamental frequency.

Japanese Patent No. 3,270,917 (Claims 1, 2, 2, 4) Japanese Patent Application No. 2003-135434 (0006)

An object (object) of the present invention is to provide a pulse photometer that reduces the processing load of processing by processing two identical signals extracted from the same medium almost simultaneously to extract a common signal component.
Further, by applying the signal processing method, the concentration of the target substance is accurately measured even when noise due to body movement of the medium is generated in the pulse wave signal.
In addition, even when noise due to body motion occurs in the pulse wave data signal, the noise is removed from the pulse wave signal and the pulse is accurately obtained.

In order to solve the above problems, a pulse photometer according to the present invention includes a light emitting means for irradiating light of two different wavelengths to the same biological tissue, and a transmission or reflection generated from the light emitting means and transmitted through the same biological tissue. A light receiving means for converting the light of each wavelength into an electrical signal, and discrete time-series pulse wave data of two wavelengths obtained from the electrical signal converted by the light receiving means, respectively, with a vertical axis or a horizontal axis 2 Based on the norm ratio calculation means for obtaining the norm value for each pulse wave data of each wavelength developed in the two-dimensional orthogonal coordinates, and further calculating the ratio of the norm values, and the norm ratio calculated by the norm ratio calculation means, Blood oxygen concentration calculating means for determining the concentration of oxygen in the blood. (Claim 1)

In the reference example,
A step of expanding two signals of a predetermined period extracted from the same medium on a two-dimensional orthogonal coordinate, and using the rotation matrix to determine the expanded signal based on a predetermined angle or a predetermined condition The two signals are processed by rotating to a predetermined angle.
With this signal processing method, it is possible to reduce the calculation processing burden of processing two identical signals extracted from the same medium almost simultaneously and extracting a common signal component.
As a result of the signal processing, the fundamental frequency of the signal main component is obtained.
With this configuration, it is possible to easily obtain a fundamental waveform with reduced noise.
An input means for inputting two signals from the same medium, a developing means for expanding two signals for a predetermined period input from the input means on two-dimensional orthogonal coordinates, and the expanded data in advance And a processing means for processing using a rotation matrix that rotates to a predetermined angle or a predetermined angle based on a predetermined condition.
With this configuration, it is possible to easily acquire a waveform with reduced noise by processing using a rotation matrix.

A pulse photometer comprising light emitting means for irradiating a living tissue with light of two different wavelengths, and light receiving means for converting light of each wavelength generated from the light emitting means and transmitted or reflected by the biological tissue into an electrical signal In
Processing means for processing the pulse wave data obtained from the electrical signals of the respective wavelengths using a rotation matrix that rotates the data to a predetermined angle or an angle determined based on a predetermined condition. And
With this configuration, it is possible to easily acquire a waveform with reduced noise by processing pulse wave data using a rotation matrix.
The pulse wave data is an electrical signal obtained from light reception signals of two wavelengths received at substantially the same point, developed into two-dimensional orthogonal coordinates with the two wavelengths as vertical and horizontal axes, respectively. It is characterized by.
The pulse wave data is for a predetermined time and is processed by moving with time.
A pulse photometer comprising light emitting means for irradiating a living tissue with light of two different wavelengths, and light receiving means for converting light of each wavelength generated from the light emitting means and transmitted or reflected by the biological tissue into an electrical signal The pulse wave signal obtained from the electrical signal of each wavelength is expanded into a two-dimensional orthogonal coordinate with each wavelength as a vertical axis or a horizontal axis, and the region projected onto the vertical axis or the horizontal axis is maximum or minimum. And a second processing means for performing processing by rotating using a rotation matrix so as to satisfy any of the following conditions.

A light emitting means for irradiating a living tissue with light of two different wavelengths, a light receiving means for converting light of each wavelength generated by the light emitting means and transmitted or reflected by the biological tissue into an electrical signal, and the light receiving section. A waveform obtained by processing pulse wave data of each wavelength of each wavelength, which is developed into two-dimensional orthogonal coordinates having the pulse wave signals of the two wavelengths respectively having a vertical axis or a horizontal axis, using a rotation matrix that rotates the wave to a predetermined angle. A waveform acquisition means for obtaining a waveform, a waveform analysis means for obtaining a fundamental frequency or pulse rate of a pulse wave by frequency analysis of the waveform obtained by the waveform acquisition means, and a concentration of a light-absorbing substance in the blood from the output of the waveform analysis means A pulse photometer comprising blood light-absorbing substance concentration calculating means for obtaining a blood pressure.
The blood light-absorbing substance concentration calculating means calculates at least one of oxygen saturation, special hemoglobin concentration, or injected dye concentration in arterial blood.

According to the pulse photometer of the first aspect, the oxygen concentration in the blood can be accurately obtained from the norm ratio obtained from the pulse wave data of each wavelength.
In addition, according to the pulse photometer, at least one of oxygen saturation, special hemoglobin concentration, or injected dye concentration in arterial blood can be calculated.

  According to the pulse photometer of the reference example, it is possible to acquire a waveform with reduced noise by processing pulse wave data using a rotation matrix.

  According to the pulse photometer of the reference example, the pulse wave data is processed using a rotation matrix to obtain a waveform with reduced noise, and the basic frequency or pulse rate of the pulse wave data is accurately obtained from the waveform. Can do.

  According to the pulse photometer of the reference example, it is possible to determine a rotation angle suitable for removing noise from the pulse wave data using a rotation matrix, and the noise is reduced by processing with the rotation matrix of the determined rotation angle. Waveform can be acquired.

  According to the pulse photometer of the reference example, it is possible to determine a rotation angle suitable for removing noise from the pulse wave data using a rotation matrix, and the noise is reduced by processing with the rotation matrix of the determined rotation angle. The basic frequency or pulse rate of the pulse wave data can be accurately obtained from the waveform.

  According to the pulse photometer of the reference example, the rotation angle of the rotation matrix can be easily determined.

According to the pulse photometer of the reference example, the pulse wave data is processed by using a rotation matrix to obtain the accurate fundamental frequency or pulse rate of the pulse wave by using a waveform with reduced noise, and oxygen saturation in arterial blood At the same time, at least one calculation of the degree, the special hemoglobin concentration, or the injected dye concentration can be processed and output almost simultaneously.
According to the pulse photometer of the reference example, at least one of oxygen saturation, special hemoglobin concentration, or injected dye concentration in arterial blood can be calculated.

It is a block diagram which shows schematic structure of this invention. It is a figure which shows the detected pulse wave. 10 is a graph in which infrared light IR data shown in FIG. 9 is plotted on the horizontal axis and red light R data is plotted on the vertical axis. FIG. 4 is a diagram obtained by rotating the graph of FIG. 3 by π / 30 [rad]. It is a figure which shows the waveform of the pulse wave processed by the rotation matrix of rotation angle 9π / 30 [rad]. It is a figure which shows the spectrum of the waveform of X1 shown in FIG. It is a flowchart which shows the processing flow in a 1st Example. It is a flowchart which shows the processing flow in a 2nd Example. It is a wave form diagram explaining the measurement principle of the fluctuation | variation of the light absorbency of the light absorption substance in the blood. It is a flowchart which shows the processing flow in a 3rd Example. It is a flowchart which shows the processing flow in a 4th Example.

In describing an embodiment of the present invention, the principle will be described by taking a pulse oximeter for measuring arterial blood oxygen saturation as an example.
The technique of the present invention is not limited to a pulse oximeter, and a blood photoabsorbing substance such as special hemoglobin (carbon monoxide hemoglobin, Met hemoglobin, etc.) or a dye injected into blood is used by the principle of pulse photometry. It can be applied to a measuring device (pulse photometer).

The configuration of the pulse oximeter for measuring arterial blood oxygen saturation is as shown in FIG. 1, which is a schematic configuration block diagram.
The light-emitting elements 1 and 2 that emit light of different wavelengths are driven by the drive circuit 3 so as to emit light alternately.
The light used for the light-emitting elements 1 and 2 is infrared light that is less affected by arterial oxygen saturation (
For example, 940 [nm]), red light (eg, 660 with high sensitivity to changes in arterial oxygen saturation)
[nm]) is good.

Light emitted from the light emitting elements 1 and 2 is transmitted through the living tissue 4, received by the photodiode 5, and converted into an electrical signal.
The reflected light may be received.
These converted signals are amplified by the amplifier 6 and distributed by the multiplexer 7 to the filters 8-1 and 8-2 corresponding to the respective optical wavelengths.
The signals distributed to the filters are filtered by the filters 8-1 and 8-2 to reduce noise components, and are digitized by the A / D converter 9.

Each signal sequence corresponding to digitized infrared light and red light forms a respective pulse wave signal.
Each digitized signal sequence is input to the processing unit 10, processed by a program stored in the ROM 12, the oxygen saturation SpO 2 is measured, and the value is displayed on the display unit 11.

<Noise reduction by rotation matrix and calculation of fundamental frequency of pulse wave>
First, measurement of the change in absorbance (light attenuation) of a light-absorbing substance in blood will be described.
FIGS. 9A and 9B are pulse wave data in which the light emitted from the light emitting elements 1 and 2 is transmitted through the living tissue 4 and received by the photodiode 5 and converted into an electrical signal. a) shows red light, and (b) shows infrared light.
In (a) of FIG. 9, assuming that the horizontal axis is time and the vertical axis is the received light output, the received light output from the photodiode 5 is obtained by superimposing the direct current component (R ′) and the pulsating component (ΔR ′) of red light. It has a waveform.
Further, in FIG. 9B, when the horizontal axis is time and the vertical axis is the light reception output, the light reception output of the photodiode 5 includes the direct current component (IR ′) and the pulsation component (ΔIR ′) of infrared light. The waveform is superimposed.
FIG. 2 shows the ratio (IR = ΔIR ′ / IR ′) of pulsating components (ΔR ′, ΔIR ′) to DC components (R ′, IR ′) for 8 seconds in the pulse wave as shown in FIG. In addition, the average value of the data for 8 seconds is set to zero.
Note that the calculation is possible without performing the process of setting the average value to zero as shown in FIG.
FIG. 3 is a graph in which the infrared light IR data shown in FIG. 9 is plotted on the horizontal axis and the red light R data is plotted on the vertical axis.

Next, calculation processing for reducing noise using two rotation wave data signals of two wavelengths digitized by the A / D converter 9 will be described.
In addition, since infrared light and red light are alternately emitted, they are not emitted at the same time. However, adjacent infrared light reception values and red light reception values obtained at the same time were obtained. The pulse wave signal of infrared light and the pulse wave signal of red light for a predetermined time are developed on a two-dimensional orthogonal coordinate.
That is, the graph of FIG. 3 is created.
Further, by taking the ratio of the pulsating component to the DC component of the pulsating wave, the absorbance pulsation due to the pulse is approximated.
The transition shown in the graph of FIG. 3 is not 45 degrees because the difference between the amplitude of the pulsating component of the infrared light pulse wave and the amplitude of the pulsating component of the red light pulse wave is due to noise. This is because is superimposed.

Next, a rotation calculation is performed on the developed pulse wave data using a rotation matrix.
A data string of the ratio (IR) of the pulsating component to the direct current component of the infrared light pulse wave,

  A data string of the ratio (R) of the pulsating component to the direct current component of the red light pulse wave is

And
Data of IR and R obtained at the same time ti is defined by a matrix as follows.
That is,

Further, if the rotation matrix for rotating θ [rad] is A, A can be expressed as follows.

  Then, the following X is obtained by rotating S by θ [rad] by A.

In addition to the above, the rotation matrix A is

May be used.
Here, a graph obtained by rotating the pulse wave data S by π / 30 [rad] from 0 to 9π / 30 [rad] is shown in FIG.
As can be seen from FIG. 4, the image is rotated around a point with zero horizontal axis and zero vertical axis (a point where both the red light pulse wave and the infrared light pulse wave are average), and θ is 9π / 30 [ rad], horizontal axis (X1)
The area projected onto the vertical axis is the smallest, and the area projected onto the vertical axis (X2) is the largest.
θ is further rotated by π / 2 [rad] from 9π / 30 [rad] to 24π / 30 [rad] (= 12π /
It is clear that the region projected onto the horizontal axis (X1) is maximized and the region projected onto the vertical axis (X2) is minimized when rotated by 15 [rad]).

Next, the measured pulse wave data S is processed into X by the rotation matrix A when θ is 9π / 30 [rad] and 24π / 30 [rad]. Explain how.
FIG. 5 shows a waveform of X obtained by processing the pulse wave data S shown in FIG. 2 by the rotation matrix A with θ being 9π / 30 [rad].
X1 (ti) where the area projected onto the horizontal axis is minimized is

  On the other hand, X2 (t i) where the area projected onto the horizontal axis is maximized is

Is calculated by
It can be seen from the waveform of X1 in FIG. 5 that noise has been removed.
When the pulse wave data S is processed by the rotation matrix A with θ being 24π / 30 [rad], the waveform of X2 is a waveform from which noise is removed.
X1 (ti) that maximizes the area projected on the horizontal axis is

On the other hand, X2 (t i) that minimizes the area projected onto the horizontal axis is

Is calculated by
If the rotation angle θ is set so that the region projected onto the horizontal axis in this way is minimized and the pulse wave data S is processed, a pulse wave main component waveform with suppressed noise can be obtained.

Next, calculation of the fundamental frequency of the pulse wave will be described.
FIG. 6 shows the spectrum obtained by frequency analysis of the pulse wave signal shown in FIG. 2 before the noise is reduced and the pulse wave main component waveform whose noise is reduced using the rotation matrix.
The horizontal axis is frequency and the vertical axis is spectrum.
The spectrum of the pulse wave (Before-rotation) signal before the noise is reduced has a strong spectrum in the frequency band fn of the noise, and the spectrum of the fundamental frequency fs of the pulse wave signal hardly appears.
On the other hand, in the spectrum obtained by frequency analysis of a pulse wave main component waveform (after-rotation) in which noise is reduced using a rotation matrix, the spectrum of the fundamental frequency fs of the pulse wave signal is the spectrum of the noise frequency band fn. The fundamental frequency fs of the pulse wave signal can be obtained.
If the fundamental frequency fs [Hz] of the pulse wave signal is obtained, the pulse rate fs × 60 [times / min] can be easily obtained.

Thus, by using a rotation matrix of a predetermined angle, a pulse wave main component waveform with reduced noise can be obtained, and the fundamental frequency or pulse rate of the pulse wave signal can be obtained.
Here, the predetermined angle may be determined in advance or may be changed adaptively during the measurement period.

<Calculation of oxygen saturation>
FIG. 3 is a graph in which the infrared light IR data shown in FIG. 9 is plotted on the horizontal axis and the red light R data is plotted on the vertical axis, as described above. The slope of this graph is expressed using the norm ratio. Ask.
First, the L2 norm of the infrared light pulse wave data IR is obtained.
Since the infrared light pulse wave data string is IR = [IR (ti): ti = 0, 1, 2, 3,...] (1), the L2 norm can be expressed by the following equation.

Next, the L2 norm of the red light pulse wave data R is obtained.
Since the red light pulse wave data string is R = [R (ti): ti = 0, 1, 2, 3,...] (2), the L2 norm can be expressed by the following equation.

Therefore,

Φ correlates with the oxygen saturation SpO2, so if the function representing the correlation is f,

The oxygen saturation SpO2 can be obtained.
A straight line with the norm ratio as an inclination is shown in FIG.
The norm is one of mathematical concepts, and the Euclidean-norm or square norm maps the size of a vector having n elements to a scalar quantity.
As described above, the oxygen saturation SpO2 can be obtained based on the ratio of the L2 norm value (square norm) of the red light pulse wave data R and the L2 norm value of the infrared light pulse wave data for a predetermined period.
Here, it is preferable to use the red light pulse wave data R and the infrared light pulse wave data IR for a predetermined period from the current pulse wave obtained sequentially to the past for a predetermined period.
Further, although the L2 norm is used as the norm value, a norm value obtained by another calculation method may be used.

Regarding the calculation of oxygen saturation,
If the noise signal is relatively small with respect to the pulse wave signal, it may be calculated using the norm ratio, but if the noise signal is relatively large, separately from the method of obtaining using the norm ratio, Japanese Patent Application 20
In place of the fundamental frequency obtained by using the frequency analysis described in 01-332383, calculation can also be performed using the fundamental frequency obtained by the processing by the rotation.

(First embodiment)
Next, an apparatus using the above principle will be described with reference to a schematic configuration block diagram and a processing flow.
The schematic block diagram is the same as FIG. 1 described above.
By being driven by the drive circuit 3 so as to emit light alternately from the light emitting elements 1 and 2,
Different wavelengths of light are emitted.
Light emitted from the light emitting elements 1 and 2 is transmitted through the living tissue 4 and received by the light receiving unit (photodiode) 5 and converted into an electric signal.
These converted signals are amplified by the amplifier 6 and distributed by the multiplexer 7 to the filters 8-1 and 8-2 corresponding to the respective optical wavelengths.
The signals distributed to the filters are filtered by the filters 8-1 and 8-2 to reduce noise components, and are digitized by the A / D converter 9.
Each signal sequence corresponding to digitized infrared light and red light forms a pulse wave.
Each digitized signal sequence is input to the processing unit 10 and processed by a program stored in the ROM 12, and the pulse rate PR and oxygen saturation SpO2 are calculated.
1 is displayed.

Next, a processing flow for calculating the pulse rate PR and the oxygen saturation SpO2 will be described with reference to FIG.
When the measurement is started (step S1), the red light pulse wave and the infrared light pulse wave are detected as described above (step S2), and each digitized signal sequence (each pulse wave data) is processed by the processing unit 10. Is taken in.
In the processing unit 10, each pulse wave data is processed as follows while reading / writing data of the process in the RAM 13 by a program stored in the ROM 12.

First, the ratio of the pulsating component to the direct current component of the pulse wave of each of the infrared light pulse wave and the red light pulse wave is obtained for each pulse wave. (Step S3)
Next, processing for determining the pulse rate PR (steps S4 to S6) and processing for determining the oxygen saturation SpO2 (steps S7 to S9) are performed simultaneously.

In the process of calculating the pulse rate PR (steps S4 to S6),
From the data S of the infrared light pulse wave data IR and the red light pulse wave data R, a waveform with reduced noise is obtained from Equation 5 by the rotation matrix A in which the rotation angle is set in advance. (Step S4)
The rotation angle to be set is projected in the axial direction as shown in FIG. 4 by rotating a graph having the infrared light pulse wave data IR as shown in FIG. 3 and the red light pulse wave data R as the vertical axis. The angle is such that the area is minimized.
For example, the rotation angle is preferably 9π / 30 [rad] or 24π / 30 [rad].
The waveform with reduced noise can be obtained from the data of the axis component that minimizes the projection area.
Then, the frequency analysis of the waveform with reduced noise is performed as shown in FIG. 6 to obtain the fundamental frequency of the pulse wave data. (Step S5)
Then, the pulse rate fs is obtained from the fundamental frequency by fS × 60 [times / min], and the display unit 11
To display.

In the process of obtaining the oxygen saturation SpO2 (steps S7 to S9), the respective L2 norm values are obtained from the infrared light pulse wave data IR and the red light pulse wave data R for a predetermined period from the expressions 10 and 11, and The ratio of the respective L2 norm values is obtained from Equation 12.
Next, the ratio of the pulse wave signal of the infrared light and the red light from which noise is removed is obtained, and the oxygen saturation is calculated.
(Step S7)
Using the L2 norm ratio as Φ, the oxygen saturation SpO2 is obtained from Equation 12 (step S8).
Is displayed on the display unit 11. (Step S9)

When the measurement is continued, the process returns to step S2 and is repeated. When the measurement is not measured, the measurement is terminated. (Step S11)

(Second embodiment)
Next, another second embodiment will be described with reference to FIG.
The difference between the second embodiment and the first embodiment is that the rotation angle is not determined in advance in step S4, but the rotation angle is obtained from the obtained data. As shown in FIG. Processing is divided into S4-1 and step S4-2.
The other steps are the same as those in the first embodiment, and a description thereof will be omitted.

In the process of calculating the pulse rate PR (steps S4-1 to S6),
First, a graph as shown in FIG. 3 is drawn using data of infrared light pulse wave data IR and red light pulse wave data R for a predetermined period.
Then, what rotation angle is used to determine the minimum projected area in the axial direction. (
Step S4-1)
Next, the pulse wave data of each wavelength is processed by the rotation matrix based on the obtained rotation angle, and a waveform with reduced noise is obtained from the axis component data that minimizes the projection area. (Step S4
-2).
As described above, the feature of the second embodiment is that the rotation angle of the rotation matrix is not a fixed angle but has an adaptive property that is changed in time according to the detected pulse wave data.

(Third embodiment)
Next, FIG. 10 shows a processing flow for calculating the pulse rate PR and the oxygen saturation SpO2 using the fundamental frequency obtained by the processing by the rotation in place of the fundamental frequency obtained by frequency analysis.
Will be described.
When the measurement is started (step S1), the red light pulse wave and the infrared light pulse wave are detected as described above (step S2), and each digitized signal sequence (each pulse wave data) is processed by the processing unit 10. Is taken in.
In the processing unit 10, each pulse wave data is processed as follows while reading / writing data of the process in the RAM 13 by a program stored in the ROM 12.

First, the ratio of the pulsating component to the direct current component of the pulse wave of each of the infrared light pulse wave and the red light pulse wave is obtained for each pulse wave. (Step S3)
Next, processing for determining the pulse rate PR (steps S4 to S6) and processing for determining the oxygen saturation SpO2 (steps S7 to S9) are performed simultaneously.

In the process of calculating the pulse rate PR (steps S4 to S6),
From the data S of the infrared light pulse wave data IR and the red light pulse wave data R, a waveform with reduced noise is obtained from Equation 5 by the rotation matrix A in which the rotation angle is set in advance. (Step S4)
The rotation angle to be set is projected in the axial direction as shown in FIG. 4 by rotating a graph having the infrared light pulse wave data IR as shown in FIG. 3 and the red light pulse wave data R as the vertical axis. The angle is such that the area is minimized.
For example, the rotation angle is preferably 9π / 30 [rad] or 24π / 30 [rad].
The waveform with reduced noise can be obtained from the data of the axis component that minimizes the projection area.
Then, the frequency analysis of the waveform with reduced noise is performed as shown in FIG. 6 to obtain the fundamental frequency of the pulse wave data. (Step S5)
Further, the pulse rate fs is obtained from the fundamental frequency from fS × 60 [times / min] and displayed on the display unit 11.

In the process of obtaining the oxygen saturation SpO2 (steps S7 to S9),
A signal from which noise is removed is obtained by passing a pulse wave signal of infrared light and red light at the fundamental frequency or through a filter composed of the fundamental frequency and its harmonics. (Step S7)
Next, the ratio of the pulse wave signal of infrared light and red light from which noise has been removed is obtained, and the oxygen saturation is calculated (step S8) and displayed on the display unit 11. (Step S9)

When the measurement is continued (step S10), the process returns to step S2 and is repeated. When the measurement is not measured, the measurement is terminated. (Step S11)

(Fourth embodiment)
Furthermore, another 4th Example is described using FIG.
The difference between the fourth embodiment and the third embodiment is that the rotation angle is not predetermined in step S4, but the rotation angle is obtained from the obtained data. As shown in FIG. Processing is divided into S4-1 and step S4-2.
The other steps are the same as those in the third embodiment, and a description thereof will be omitted.

In the process of calculating the pulse rate PR (steps S4-1 to S6),
First, a graph as shown in FIG. 3 is drawn using data of infrared light pulse wave data IR and red light pulse wave data R for a predetermined period.
Then, what rotation angle is used to determine the minimum projected area in the axial direction. (
Step S4-1)
Next, the pulse wave data of each wavelength is processed by the rotation matrix based on the obtained rotation angle, and a waveform with reduced noise is obtained from the axis component data that minimizes the projection area. (Step S4
-2).
As described above, the feature of the fourth embodiment is that the rotation angle of the rotation matrix is not a fixed angle, but has an adaptive property that is changed in time according to the detected pulse wave data.

The pulse oximeter for measuring arterial blood oxygen saturation has been described above as an example. However, the technique of the present invention is not limited to the pulse oximeter, and special hemoglobin (carbon monoxide hemoglobin, Met hemoglobin, etc.), The present invention can also be applied to an apparatus (pulse photometry) that measures a blood light-absorbing substance such as an injected dye using the principle of pulse photometry by selecting the wavelength of the light source.
In this specification, a signal measured via a living tissue (medium) is described as a “pulse wave signal” before being expanded to two-dimensional orthogonal coordinates, and before being expanded to two-dimensional orthogonal coordinates. , “Pulse wave data”, and the obtained waveform is distinguished from “pulse wave main component waveform”.

According to the present invention, it is possible to realize signal processing that reduces the calculation processing burden of processing two similar signals extracted from the same medium almost simultaneously and extracting a common signal component.
In the present invention, the concentration of the target substance can be accurately measured even when noise due to body movement of the medium occurs in the pulse wave signal.
In addition, even if noise due to body movement occurs in the pulse wave data signal, the noise can be removed from the pulse wave signal, and the concentration of the light-absorbing substance in the pulse and blood can be obtained with high accuracy. The availability is extremely large.

DESCRIPTION OF SYMBOLS 1 Light emitting element 2 Light emitting element 3 Drive circuit 4 Living body tissue 5 Photodiode 6 Converter 7 Multiplexer 8 Filter 9 A / D converter 10 Processing part 11 Display part 12 ROM
13 RAM

Claims (1)

A light emitting means for irradiating the same biological tissue with light of two different wavelengths;
A light receiving means for converting light of each wavelength generated from the light emitting means and transmitted or reflected through the same living tissue into an electrical signal;
About each pulse wave data of each wavelength developed in two-dimensional orthogonal coordinates with the vertical axis or the horizontal axis of discrete time series pulse wave data of two wavelengths obtained from the electrical signal converted by the light receiving means A norm ratio calculating means for obtaining a norm value and further obtaining a ratio of the norm values;
A pulse photometer comprising blood oxygen concentration calculating means for obtaining a blood oxygen concentration based on the norm ratio calculated by the norm ratio calculating means.

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