JPH11323A - Noninvasive blood analyzing device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To non-invasively measure the size of a blood vessel or the concentration of blood components for one and the same subject. SOLUTION: This analyzing device includes a light source part 11 for illuminating a part of a living body involving blood vessels, a photographing part 12 which photographs the part of the living body illuminated, a holding member for holding the light source part 11 and the photographing part 12 against the part of the living body, an analyzing part 2 which sets an analytical area in the image photographed and which measures and analyzes blood vessel parts in the analytical area, and a display part which displays the result of the analysis, the photographing part 12 photographing the part of the living body plural times, the analyzing part 2 specifying the analytical area involving one and the same blood vessel part for the plurality of photographed images, and calculating at least either one of blood vessel width, the concentration of blood components, or the concentration ratio of blood components in the blood vessel part in the analytical area specified.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a non-invasive blood analyzer, and percutaneously without blood collection.
Provided is an apparatus for measuring a blood vessel size, a blood component concentration, and a blood component concentration ratio in real time with good reproducibility.

[0002]

2. Description of the Related Art A technique for directly measuring a blood vessel width using an image is performed on microcirculation (especially blood vessels on the retina) (for example, MJ).
DEVANEY et al., “Continuous Measurement of Vascular D
iameters via Television Microscopy ”ISA TRASRATIO
N, Vol. 15, No. 1, pages 73-78, 1976). However, since this technique targets a blood vessel of several tens of μm, it is not suitable for actual clinical use.

[0003] Further, a device for percutaneously measuring hemoglobin concentration and hematocrit has been devised. For example, "Hemoglobin concentration measuring device"
Japanese Patent Application Laid-Open No.-71135) discloses a device that irradiates a living body with light of a plurality of wavelengths and measures blood hemoglobin from a change in light intensity due to the pulsation. Similarly, "System and
"Method for noninvasive hemarocrit monitoring" (US Pat. No. 5,372,136) also describes a method for determining blood hematocrit using pulsation or the like.

However, since the amount of blood to be detected is not specified, there is a problem in terms of accuracy in obtaining an absolute value. Furthermore, it is expected that there will be a difference in the measured value depending on the part where the sensor is mounted, and there will be a problem in reproducibility and the like.

[0005] Also, "Apparatus and method for in vi
vo analysis of RED and WHITE blood cell indices ''
(U.S. Pat. No. 4,998,533) discloses a method for measuring the above items from a red blood image flowing through a capillary, but such a method requires an extremely large-scale system.

[0006] Also, various non-invasive blood analyzers as described below are known. That is, an image of a blood vessel contained in a part of a living body is taken, and the form and number of blood cells are analyzed from the taken image (US Pat. No. 5,598,842).
Or Japanese Patent Application Laid-Open No. 7-308312), in which a blood vessel contained in a part of a living body is imaged a plurality of times, and a blood cell image is detected from a difference image thereof (Japanese Patent Application Laid-Open No. 7-30831).
No. 1), means for imaging a blood vessel contained in a part of a living body through a transparent plate adhered to the skin surface of a living body, and the transparent plate is mechanically moved along the skin surface. A blood vessel of a desired size is searched for and imaged (see Japanese Patent Application Laid-Open No. 8-299310), a blood vessel and a tissue contained in a part of a living body are imaged, and the imaged image is distributed across the blood vessel. For calculating the amount of blood components from an image density distribution (see International Patent Application Publication No. WO
97/24066).

When a part of a living body is imaged with time using such a non-invasive blood analyzer to determine a temporal change in an analysis value, the imaging device is separated from the living body after imaging once. After a time or several days, a part of the living body will be imaged again. However, since reproducibility of a vascular site to be imaged is not guaranteed, it has been difficult to accurately obtain an analysis value for the same vascular site.

[0008] The present invention has been made in view of such circumstances, and in a plurality of images taken over time,
By identifying and analyzing the analysis region including the same blood vessel site, the time-dependent analysis value for the same blood vessel site can be obtained with high accuracy, such as changes to various stimuli such as exercise and dialysis for the subject, drug administration, etc. The purpose of the present invention is to provide a blood analyzer capable of knowing the effect on the blood analyzer.

[0009]

SUMMARY OF THE INVENTION The present invention relates to a light source unit for illuminating a part of a living body including a blood vessel, an imaging unit for imaging a part of the illuminated living body, and a light source unit and an imaging unit. A holding member for holding a part of the analysis part, an analysis part for setting an analysis area in the captured image, measuring and analyzing a blood vessel part in the analysis area, and a display for displaying the analysis result The imaging unit captures a part of the living body a plurality of times, the analysis unit identifies an analysis region including the same blood vessel region in the plurality of captured images, and sets a blood vessel width in the blood vessel region in the identified analysis region. A non-invasive blood analyzer which calculates at least one of a blood component concentration and a blood component concentration ratio.

[0010]

BEST MODE FOR CARRYING OUT THE INVENTION In the apparatus of the present invention, a living body is a mammal including a human, and a part of the living body is not a tissue separated from the living body but a part of a living tissue of the living body. Examples include fingers and earlobes.

The light source section includes a semiconductor laser (hereinafter, LD)
Or an LED or a halogen light source can be used. The light may be directly applied to a part of the living body, or may be applied via a fiber. The wavelength is preferably in the range of 600 to 950 nm, which transmits through the living tissue and does not absorb much water.

The imaging section can be composed of an optical system such as a lens and an imaging device such as a CCD. In the imaging unit, density distribution information of a blood vessel portion is obtained. As an image sensor, CC
In addition to D, a line sensor or a photodiode array can be used. Alternatively, one photodiode can be driven in a direction crossing a blood vessel to obtain density distribution information.
To image a part of the living body a plurality of times means to image a plurality of times at one wavelength or to image at least once for each wavelength at a plurality of wavelengths.

[0013] The optical system of the image pickup section may be constituted by merely providing a TV lens (for example, BD1214D made by COMICAR).
When the light source unit illuminates a part of the living body, the imaging unit can receive the transmitted light or the reflected light and image the part of the living body.

The holding member for holding the light source unit and the imaging unit to a part of the living body may be provided between the light source unit and the imaging unit when the living body is a finger of a human hand, for example. Any member that can fix the finger so that it can be detached, such as a method that inserts a finger into a hole or a groove that matches the shape of the finger, or a method that sandwiches a finger from both sides with a movable piece Can be used.

In this case, it is preferable that the finger is fixed with good reproducibility to the position of the light source and the image pickup unit. However, if the finger is tightened or bent too strongly, the blood vessel is compressed and congested, and the normal blood vessel becomes congested. Care must be taken because images and measurement results cannot be obtained.

The analyzing section in the apparatus according to the present invention, wherein the analyzing section stores, for each captured image, a feature extracting section for extracting a morphological feature of a part of a living body in the image, and stores the extracted features. A feature storage unit, a comparison unit that compares each feature in the captured image, and an analysis region setting unit that specifies a region including the same blood vessel site in a plurality of images based on the comparison result and sets the region as an analysis region. The blood vessel portion in the analysis region may be configured to include at least one of a blood vessel width, a blood component concentration, and a blood component concentration ratio. A commercially available personal computer can be used for this.

Some of the morphological features of the living body are the outline of the finger,
It is preferably based on at least one of the joint contour and the blood vessel arrangement pattern. The imaging unit may image a part of the living body multiple times over time, and the analysis unit may display the blood vessel width, blood component concentration, or blood component concentration ratio obtained from the plurality of images on the display unit as a change over time. Good. The analysis unit
This change over time may be displayed on a display unit as a graph.

The blood component concentration in the device of the present invention is, for example, hemoglobin concentration or hematocrit. In this case, it is preferable to use a wavelength (for example, 805 nm) or a wavelength band in which the absorbance of oxyhemoglobin and reduced hemoglobin becomes substantially equal to each other.

It is preferable that the light source section comprises a light emitting element for selectively emitting light of the first and second wavelengths or light of three or more wavelengths. The first and second wavelengths are determined based on hemoglobin concentration and hematocrit. For measurement, it is desirable to have substantially equal absorption wavelengths of oxyhemoglobin and reduced hemoglobin, respectively. The third wavelength may be such that the absorption of reduced hemoglobin is sufficiently greater than the absorption of oxidized hemoglobin. This makes it possible to measure the oxygenation rate of hemoglobin (the ratio of the oxygenated hemoglobin concentration to the total hemoglobin concentration).

In order to measure hemoglobin, hematocrit, or oxygenation rate, two or more wavelengths are required. However, when monitoring the size of a blood vessel, only one wavelength may be used.

The light source comprises a light source that emits light having a wavelength at which the absorption of oxyhemoglobin and the absorption of reduced hemoglobin are substantially equal. The analysis unit calculates the image density distribution of the portion crossing the blood vessel in the captured image, and calculates the image density. The blood vessel width may be calculated based on the distribution.

The light source comprises a light source which emits two wavelengths at which absorption of oxyhemoglobin and absorption of reduced hemoglobin are substantially equal, and the analyzing unit comprises a blood vessel in an analysis region of each image obtained by imaging with light of each wavelength. May be calculated, and the hemoglobin concentration or hematocrit may be calculated based on the image density distribution.

The light source comprises a light source that emits light having a wavelength at which absorption of oxyhemoglobin and absorption of reduced hemoglobin are substantially equal and light having a wavelength at which absorption of reduced hemoglobin is sufficiently larger than absorption of oxyhemoglobin. The ratio of the oxyhemoglobin concentration to the total hemoglobin concentration may be calculated based on the image density distribution of the portion crossing the blood vessel in the analysis region of each image obtained by imaging with light of the wavelength. In the present invention, the concentration of biochemical substances such as glucose, cholesterol, and bilirubin can be analyzed.

According to another aspect of the present invention, a part of a living body including a blood vessel is illuminated, a part of the illuminated living body is imaged a plurality of times, and a part of the living body in the image is taken for each captured image. The morphological features of the part are extracted, the extracted features are compared, a region including the same vascular site is identified in a plurality of images based on the comparison result, and the vascular width and blood component of the vascular site in the specified region are determined. It is an object of the present invention to provide a blood analysis method characterized by calculating at least one of a concentration and a blood component concentration ratio.

Hereinafter, the present invention will be described in detail based on an embodiment shown in the drawings. This does not limit the present invention. FIG. 1 is a block diagram showing the configuration of the analyzer according to the present invention, which can selectively execute a "blood vessel width measurement mode", a "blood component concentration measurement mode", and an "oxygenation rate measurement mode". In FIG. 1, a detection unit 1 captures a light source unit 11 for illuminating a part of a living body including a blood vessel (here, a human finger) and a light image of the illuminated living body part (a transmitted light image here). The imaging unit 12 is provided.

When the image capturing section 12 captures a part of a living body a plurality of times, the analyzing section 2 provides, for each captured image, a positional characteristic of a part of the living body in the image (here, the first joint position of the finger). A feature extraction unit 31 for extracting coordinates of the dent in the outline of the image, a storage unit 32 for storing the extracted features,
A comparison unit 33 that compares each feature and an analysis region setting unit 34 that specifies an analysis region including the same blood vessel region in a plurality of images based on the comparison result are provided.

Further, the analyzing unit 2 includes an extracting unit 21 for extracting, as a density profile of the image, an image density distribution of a portion which intersects a blood vessel in the analysis area at a right angle and linearly with the captured image, and an extracted density profile. A quantifying unit 22 for quantifying the morphological characteristics of the above, a calculating unit 23 for calculating the blood vessel diameter, blood component concentration, oxygenation rate, etc. based on the quantified characteristics, and a storage unit 25 for storing the calculation results. And an output unit (CRT) 24 for outputting a calculation result and a monitor image. The input unit 35 includes a keyboard and a mouse, and sets a measurement mode, initializes an analysis area, and calculates
The user inputs the calculation condition of No. 3. The analysis unit 2 is constituted by a personal computer.

FIG. 2 is a perspective view of the external appearance of the apparatus shown in FIG. 1, and the detection unit 1 and the analysis unit 2 are connected by a signal cable 3. FIG. 3 is a cross-sectional view of the detection unit 1. The detection unit 1 includes a light source unit 11 and an imaging unit 12, that is, a lens 14 and an imaging element 15. Illuminates the finger 16, and an image based on the transmitted light is captured by the image sensor 15 via the lens 14. Here, the opening 13 is provided for the finger 1 to be inserted.
The inner diameter decreases toward the fingertip so that the fixing member 6 can be fixed lightly, and constitutes a holding member.

The image pickup device 15 is constituted by a CCD. FIG. 11 is a front view of the light source unit 11 and includes an LED.
11a, an LED 11b and an LED 11c. In this embodiment, the wavelengths (first and second wavelengths) of the LEDs 11a and 11b are selected so that the absorptions for oxyhemoglobin and reduced hemoglobin are equal. LED 11c
Is selected such that the absorption of reduced hemoglobin is sufficiently larger than the absorption of oxidized hemoglobin (third wavelength). That is, L3989 (manufactured by Hamamatsu Photonics KK) having a center wavelength of 830 nm and a half value width of 40 nm is used as the LED 11a, and L2656 (manufactured by Idemitsu) having a center wavelength of 890 nm and a half value width of 50 nm is used as the LED 11b.
And an LED (manufactured by Ibid.) Having a center wavelength of 660 nm and a half-value width of 40 nm is used as the LED 11c. As described later, in the “blood vessel width measurement mode”,
Only the LED 11a is turned on, the LEDs 11a and 11b are turned on in the "blood component concentration measurement mode", and the LEDs 11a, 11b and 11c are turned on in the "oxygenation rate measurement mode".

A measurement procedure performed in such a configuration will be described. (1) Blood vessel width measurement mode In this mode, a blood vessel image is imaged a plurality of times over time using one wavelength. As shown in FIG. 4, first, the "blood vessel width measurement mode" is set by operating the input unit 35 (step S1), and the finger 16 is turned on by the LED 11a (first wavelength).
6, an image 41 including a blood vessel (vein) image 40 localized on the skin surface on the CCD 15 side is obtained together with the contour 16a of the finger 16 as shown in FIG. 6 (step S2). Next, the analysis area R1 is set in the image 41 (step S3).

The procedure for setting the analysis area R1 is executed according to the procedure shown in FIG. That is, when the measurement is the first time (step S31), a region having the best contrast of the blood vessel image 40 is searched, and the determined region is set as the analysis region R1 (step S32). Note that the analysis region R1
Is automatically set by the analysis area setting unit 34, but may be manually set by the user operating the input unit 35 while watching the monitor image output to the output unit 24.

In the set analysis area R1, the coordinates of the vertices of the quadrangle are stored in the storage unit 32, using the screen of the image 41 as the XY coordinate plane (step S33). Next, the feature extracting unit 31 extracts the joint position P1 from the depression of the contour 16a in the image 41, and stores the coordinates of the extracted position P1 in the storage unit 32 (Steps S34 and S35).

In step 31, the measurement is
In the case of the first time or later, for example, when an image 41a as shown in FIG. 7 is obtained in the previous step, the stored coordinates of the analysis region R1 are read out, and the joint position P2 is characterized from the image 41a. It is extracted by the extraction unit 31 (steps S36, S37).

Next, the coordinate difference Δ between the joint position P1 set at the time of the first measurement and the joint position P2 extracted this time is shown.
X and ΔY are calculated by the comparison unit 33 (step S
38). If none of ΔX and ΔY exceeds the predetermined allowable range δ (step S39), the analysis area setting unit 34 shifts the initially set analysis area R1 by ΔX and ΔY to set a new analysis area R2. It is set (step S40).

Thus, the blood vessel part in the region R2 becomes substantially the same as the blood vessel part in the region R1 set at the time of the first measurement. In this way, even if the finger of one subject is measured n times over time (eg, every two hours), the analysis regions R1, R2,... Rn are set each time,
Measurement is always performed on the same part of the blood vessel. In addition,
In step S39, if either ΔX or ΔY exceeds the allowable value δ, it is determined that the finger 16 is not properly set with respect to the detection unit 1 and the output unit 24 outputs an “error”.
Is displayed.

Next, in step S4 in FIG. 4, when the profile extracting unit 21 creates a density profile (FIG. 8) in a direction perpendicular to the blood vessel in the set analysis region,
The quantification unit 22 normalizes this concentration profile with a baseline. The baseline is obtained from the density profile other than the blood vessel portion by the least square method or the like, and the profile shown in FIG. 8 is normalized as shown in FIG. 9 (step S5). This makes it possible to obtain a density profile that does not depend on the amount of incident light.

The calculation unit 23 obtains the peak height h1 from the standardized density profile (FIG. 9) and calculates (1/2)
The distribution width (half width) w1 at h1 is calculated as the blood vessel width and stored in the storage unit 25 (step S6). And
When the measurement of the predetermined number of times is completed, a graph or a table showing the temporal change thereof is created and displayed from the calculated blood vessel width (steps S7 to S9).

FIG. 12 shows two fingers for one subject.
This is an example in which measurement is performed at intervals and a relative temporal change in the blood vessel width w1 is displayed on the output unit 24 as a graph. Thereby, it was possible to know how much the blood vessel width w1 changes over time. Further, the behavior of the blood vessel width with respect to exercise, dialysis, and various stimuli can be known, and is clinically useful.

(2) Blood Component Concentration Measurement Mode In this mode, an operation of imaging once for each of two wavelengths is performed a plurality of times over time. In FIG. 4, first, the "blood component concentration measurement mode" is set by operating the input unit 35 (step S11), and the LED 11a (first wavelength) and the LE are set.
D11b (second wavelength) sequentially illuminates the finger 16,
Each image is taken (steps S12 and S13), and the first
With respect to the image obtained by the wavelength, an analysis area is set by the same procedure as in step S3, that is, the procedure shown in FIG. 5 (step S14).

Next, the profile extracting section 21 performs, for each image obtained by the first and second wavelengths, the first density profile and the second density profile as shown in FIG.
Is created (step S15). The quantification unit 22 normalizes the first and second density profiles with the baseline as shown in FIGS. 9 and 10, respectively (step S16).

Therefore, the arithmetic unit 23 sets the standardized first
The peak height h1 and the half-value width w1 are calculated for the density profile (FIG. 9), and the peak height h2 is similarly calculated for the standardized second density profile (FIG. 10) (step S17). To calculate the hemoglobin concentration HGB and the hematocrit HCT (step S18).

That is, if the scattering coefficient of blood at the first wavelength is S1, the absorption coefficient is A1, and Beer's law is approximately established, log (1-h1) =-k (S1 + A1) w1 ... (1) Here, k is a proportionality constant.

By the way, the scattering coefficient S1 and the absorption coefficient A1 are
Since each is considered to be proportional to the hematocrit HCT and the amount of hemoglobin in blood, σ1 and ε1 are constants, and S1 = σ1 · HCT, A1 = ε1 · HGB (2) Therefore, log (1-h1) = − (kσ1) HCT + kε1 · HGB) · w1 (3)

Therefore, the peak height h2 obtained from the image obtained by the LED 11b (second wavelength) is similarly calculated as S2
= Σ2 · HCT, A2 = ε2 · HGB (σ2, ε2 are constants), and log (1-h2) = − k (S2 + A2) · w1 = − (kσ2 · HCT + kε2 · HGB) · w1 (4) Become. Since k, σ1, σ2, ε1, ε2 are determined theoretically or experimentally, when h1, h2, w1 are obtained,
HGB and HCT are obtained from equations (3) and (4).

By the way, since the image is actually blurred by the tissue existing from the blood vessel to the epidermis, the observed peak value is smaller than when no tissue is present. Therefore, log (1−h1) = − k (S + A) w1 + T (5) Here, S is the scattering coefficient of blood, A is the absorption coefficient of blood, and T is a term representing the effect of the living tissue.

It has been experimentally found that this T is relatively constant by selecting a portion where the contrast of the blood vessel image becomes maximum in the obtained image as an analysis region. Therefore, using T experimentally obtained, HGB,
There is no problem in finding HCT. HG calculated
B and HCT are stored in the storage unit 25. When such measurement is repeated a predetermined number of times, the arithmetic unit 23 creates and displays a graph or a table representing the change over time from the calculated values (steps S19 and S20).

FIG. 13 shows an example in which a finger of one subject is measured every two days, and the change over time of HGB and HCT is displayed on the output unit 24 as a graph. It is clinically useful because it can be used to determine the presence or absence of bleeding and the effects of diet and drug administration.

(3) Oxygenation Rate Measurement Mode In this mode, the operation of imaging once for each of a plurality of wavelengths is performed a plurality of times (over time). The “oxygenation rate measurement mode” is set by the input unit 35. Then, as shown in FIG. 14, the finger 16 is moved by the LED 11a (first wavelength: 830 nm).
Is illuminated to perform imaging (step S51). Next, LED
The finger 16 is illuminated with 11b (second wavelength: 890 nm), and an image is captured similarly (step 52). Next, LED1
The finger 16 is illuminated with 1c (third wavelength: 660 nm) and imaged (step S53). Then, the analysis area is set according to the procedure shown in FIG. 5 (step 54).

Next, each density profile of the image at the first, second and third wavelengths is created as shown in FIG.
(Step S55). Next, each density profile is standardized (step S56), and the peak heights h1, h2, h3 are set.
And the width w1 are calculated (step S57). Next, the oxygenation rate is calculated and stored in the storage unit 25 (step S5).
8). The measurement may be repeated a predetermined number of times, and a graph or table representing the change over time may be created and displayed (step S5).
9-S61).

Here, the principle of calculating the oxygenation rate in step S58 will be described. HG for total hemoglobin
B, where oxyhemoglobin is HGBo and reduced hemoglobin is HGBr, HGB = HGBo + HGBr (6)

The absorbance at the first wavelength for oxidized and reduced hemoglobin is ε1 (because of equal absorption), and the absorbance at the second wavelength for oxidized and reduced hemoglobin is ε1.
2 (because of equal absorption), the absorbances for oxidized and reduced hemoglobin at the third wavelength are ε3o and ε3r, respectively.

Further, the absorption coefficient at the first wavelength is A1, the scattering coefficient is S1, the absorption coefficient at the second wavelength is A2, the scattering coefficient is S2, the absorption coefficient at the third wavelength is A3, and the scattering coefficient is S3.
Assuming that the peak height of the density profile normalized for each wavelength is h1, h2, h3 and the width is w1, respectively, log (1-h1) = − k (A1 + S1) as in the equation (1). ) W1 (7) log (1-h2) =-k (A2 + S2) w1 (8) log (1-h3) =-k (A3 + S3) w1 (9) From (8), A1, A2, S1, S2
Is determined.

On the other hand, S3, like S1 and S2, is considered to be proportional to the hematocrit HCT of blood, and is determined as S3 = σ3 · HCT (10). Therefore, from equations (9) and (10), A
3 is also found.

A3 / A1 = (ε3o · HGBo + ε3r · HGBr) / (ε1 · HGB) (11) Since ε3r >> ε3o, A3 / A1 = ε3r · HGBr / (ε1 · HGB) = a · HGBr / HGB (12) (a = ε3r / ε1)

From the definition of the oxygenation rate, r = HGBo / HGB = 1−HGBr / HGB = 1− (1 / a) · (A3 / A1) (13), and the oxygenation rate is calculated. The clinical significance of the venous oxygenation rate is not as clear as arterial oxygen saturation at present. However, the difference between the arterial oxygen saturation and the venous oxygen saturation is the amount of oxygen actually consumed, and the venous oxygen saturation is considered to reflect the reserve amount of oxygen in the living body. It is expected that the clinical utility of the present invention will be clarified more and more specifically.

[0056]

According to the present invention, since the same blood vessel region is analyzed for a plurality of obtained images, the blood vessel width, the blood component concentration, the blood component concentration ratio, and the like can be measured with little variation factors. In addition, if a part of the living body is imaged a plurality of times with the lapse of time, it is possible to observe a detailed temporal change in the state of the subject from the images. In addition, by extracting and comparing some features of the living body using the captured image, the same blood vessel site can be specified without requiring a special mechanism.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a configuration of an embodiment of the present invention.

FIG. 2 is a perspective view showing an outer shape of the embodiment of the present invention.

FIG. 3 is a sectional view showing a main part of the embodiment of the present invention.

FIG. 4 is a flowchart showing the operation of the embodiment of the present invention.

FIG. 5 is a flowchart showing another operation of the embodiment of the present invention.

FIG. 6 is an explanatory diagram showing an example of an image obtained by the embodiment of the present invention.

FIG. 7 is an explanatory diagram showing an example of an image obtained by the embodiment of the present invention.

FIG. 8 is an explanatory diagram showing a density profile of an image according to the embodiment of the present invention.

FIG. 9 is an explanatory diagram showing a normalized density profile according to the embodiment of the present invention.

FIG. 10 is an explanatory diagram showing another normalized density profile according to the embodiment of the present invention.

FIG. 11 is a front view of the light source according to the embodiment of the present invention.

FIG. 12 is an explanatory diagram showing a display example of the embodiment of the present invention.

FIG. 13 is an explanatory diagram showing another display example of the embodiment of the present invention.

FIG. 14 is a flowchart showing still another operation of the embodiment of the present invention.

[Explanation of symbols]

 Reference Signs List 1 detection unit 2 analysis unit 11 light source unit 12 imaging unit 21 extraction unit 22 quantification unit 23 operation unit 24 output unit 25 storage unit 31 feature extraction unit 32 storage unit 33 comparison unit 34 analysis area setting unit 35 input unit

Claims (7)

[Claims] A light source unit for illuminating a part of a living body including a blood vessel; an imaging unit for imaging a part of the illuminated living body;
A holding member for holding the light source unit and the imaging unit with respect to a part of the living body, and an analysis unit that sets an analysis region in a captured image, measures and analyzes a blood vessel portion in the analysis region, A display unit for displaying the analysis result, wherein the imaging unit captures a part of the living body a plurality of times, and the analysis unit identifies an analysis region including the same blood vessel region in the plurality of captured images, and performs the identified analysis. A non-invasive blood analyzer that calculates at least one of a blood vessel width, a blood component concentration, and a blood component concentration ratio for a blood vessel site in a region. An analysis unit configured to extract, for each captured image, a morphological feature of a part of a living body in the captured image; a feature storage unit configured to store the extracted features; A comparison unit that compares each feature in, an analysis region setting unit that specifies a region including the same blood vessel region in a plurality of images based on the comparison result, and sets the region as an analysis region; and a blood vessel region within the set analysis region. About blood vessel width,
2. The non-invasive blood analyzer according to claim 1, further comprising a calculation unit that calculates at least one of a blood component concentration and a blood component concentration ratio. 3. The non-invasive body according to claim 2, wherein a part of the living body is a human finger, and the characteristic of the living body is based on at least one of the outline of the finger, the outline of the joint, and the arrangement pattern of blood vessels. Blood vessels and blood measurement devices. 4. The imaging device according to claim 1, wherein the imaging unit images a part of the living body a plurality of times over time, and the analysis unit displays a calculation result obtained from the plurality of images on the display unit as a change over time. Non-invasive blood analyzer. 5. The light source comprises a light source that emits light having a wavelength at which absorption of oxyhemoglobin and absorption of reduced hemoglobin are substantially equal, and the analysis unit calculates an image density distribution of a portion crossing a blood vessel in a captured image, 2. The non-invasive blood analyzer according to claim 1, wherein the blood vessel width is calculated based on the image density distribution. 6. The light source comprises a light source that emits light of two wavelengths, each of which has substantially the same absorption of oxyhemoglobin and the absorption of reduced hemoglobin, and the analysis unit obtains each image obtained by imaging with light of each wavelength. The non-invasive blood analyzer according to claim 1, wherein an image density distribution of a portion crossing a blood vessel in the analysis region is calculated, and a hemoglobin concentration or a hematocrit is calculated based on the image density distribution. 7. The light source comprises a light source which emits light having a wavelength at which absorption of oxyhemoglobin and absorption of reduced hemoglobin are substantially equal and light having a wavelength at which absorption of reduced hemoglobin is sufficiently larger than absorption of oxidized hemoglobin. The non-invasive blood according to claim 1, wherein the unit calculates a ratio of the oxyhemoglobin concentration to the total hemoglobin concentration based on an image density distribution of a portion crossing a blood vessel in an analysis region of each image obtained by imaging with light of each wavelength. Analysis equipment.