JP2000083932A - Noninvasive vital component measuring instrument - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a noninvasive vital component measuring instrument which is capable of displaying the time series data of the vital component information and arbitrary selection information of the same person as the results of analyses. SOLUTION: This noninvasive vital component measuring instrument has a light source section 11 for supplying light to the living body to be inspected, a photodetecting section 12 for detecting the optical information in the living body receiving the light, a data processing section 2 for executing the data processing of the optical information, an output section 24 for outputting the vital component information obtd. by the data processing and a manipulating section 35 for inputting and manipulating the data necessary for the data processing. The manipulating section 35 displays the time series data of the vital component information and arbitrary selection information which is arbitrarily selected of the same person as the results of the analyses. Further, the arbitrary selection information is the action record, exercise record and time trial record of the same person.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a non-invasive biological component measuring device for non-invasively measuring biological component information.

[0002]

2. Description of the Related Art The circulatory dynamics of living organisms are often related to behavioral and exercise performances of individuals. For example, it has been reported that blood hemoglobin concentration is useful as an index indicating aerobic (aerobic) exercise ability, because it directly reflects oxygen carrying ability.

[0003] It is necessary to measure such an index periodically, but it is difficult to measure the index frequently using a normal blood sampling method.

[0004] Therefore, a transmission image of a blood vessel fitted to a part of a living body such as a finger is obtained with a simple device configuration, and image analysis is performed to determine the blood vessel size, the hemoglobin concentration, and the concentration of blood components such as hematocrit. Devices intended for transcutaneous, non-invasive measurements have been devised (eg, International Patent Application Publication No. WO 97/24066).

[Problems to be solved by the invention]

[0005] However, such a conventional analyzer can simply display the measurement results such as the blood vessel width and the blood component concentration. However, the measurement results can be displayed in a graph or a table to display a time-series change. In addition, it cannot be displayed in connection with arbitrary selection information.

The present invention has been made in view of such circumstances, and displays, as an analysis result, time-series data of optional information corresponding to biological component information of the same person measured from a plurality of optical information. An object of the present invention is to provide a non-invasive biological component measuring device capable of performing the measurement.

[0007]

According to the present invention, there is provided a light source unit for supplying light to a living body to be inspected, a light receiving unit for detecting optical information on the living body which has received the light, and a method for transmitting the optical information to a living body. A data processing unit for processing, an output unit for outputting biological component information obtained by the data processing, and an operation unit for inputting and operating data necessary for the data processing, wherein the data processing unit is a biological component of the same person The information and time-series data of arbitrarily selected optional information are displayed on an output unit as an analysis result. Here, the optional information is an index indicating a state of a living body, and includes, for example, weight, blood pressure, heart rate, body fat percentage, and the like.

Further, the optional information is the same person's action result, exercise result, and time trial result. Here, the behavioral performance is a result or outcome produced by the behavior, and includes, for example, exercise performance, work performance, work performance, and the like. In addition, the exercise results indicate the results of exercise such as a race, a weight increase, and a javelin throw. Further, the time trial result is a time in a competition for time, and indicates, for example, the result of a time trial such as sprinting, long-distance running, and swimming.

[0009]

BEST MODE FOR CARRYING OUT THE INVENTION In the living body examination 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 tissue as it is. For example, a finger or a soft ear may be used.

[0010] The detecting section of the product of the present invention comprises a light source section, a light receiving section and a holding section. A semiconductor laser (hereinafter, LD), LED, or halogen light source can be used for the light source unit, and the light source unit may directly irradiate a part of the living body or irradiate through 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 light receiving section can be composed of an optical system such as a lens and a light receiving element such as a photodiode or a CCD. When a CCD is used as the light receiving element, density distribution information of a blood vessel portion can be obtained. As the light receiving element, a line sensor or a photodiode array can be used in addition to the CCD. Also,
The density distribution information can be obtained by driving one photodiode in a direction crossing the blood vessel.

In the case where a CCD is used as the light receiving element, the optical system of the light receiving section may be configured using only a TV lens.

[0013] In order to obtain more preferable optical information, the detecting section preferably includes a holding member for holding the light source section and the light receiving section to a part of the living body. When a part of the living body is, for example, a finger of a human hand, the holding member may be a member that detachably holds the finger between the light source unit and the imaging unit. A type in which the finger is inserted into a hole or groove corresponding to the shape of the finger, or a type in which the finger is sandwiched between the movable pieces from both sides can be used.

The analyzing section of the product of the present invention comprises a placing section, a data processing section, an output section and an operating section. The detection unit mounted on the mounting unit of the analysis unit can be directly connected to the analysis unit by a connector. These connectors have a role of a port for transmitting optical information of the detection unit as an electric signal to the analysis unit, and also a role of fixing and integrating the detection unit and the analysis unit. When the detection unit and the analysis unit are separated from each other, it can be dealt with by removing the detection unit from the mounting unit and separately providing a connection code between the detection unit and the analysis unit.

The detecting section and the analyzing section are connected in advance by a storage-type reel-type connecting cord, or
By providing a wireless transceiver such as an infrared transceiver, it is possible to separately attach and detach the mounting part of the detecting part and the analyzing part with a fixing member having irregularities, a magnet, an adhesive tape, a screw, etc. good.

The analysis section can display on the output section, as analysis results, blood-related information and time-series data of arbitrarily selected information from the obtained plurality of optical information of the same person. The information relating to blood is information relating to blood or blood flow, and specifically includes blood vessel diameter, blood component concentration (eg, hemoglobin, hematocrit, etc.), blood component concentration ratio (eg, oxygenation rate, etc.), and the like. . The arbitrarily selected information can be an indicator of the health of the same person,
There may be behavioral performance, exercise performance and time trial performance. In addition, the analysis unit, in order to analyze the optical information,
A microcomputer including a CPU, a ROM, a RAM, and an I / O port and a commercially available personal computer can be used.

The output unit can use a display device such as a CRT or a liquid crystal display, or a printing device such as a printer.

The operation unit can be composed of a keyboard or numeric keypad for inputting measurer information and measurement data.

[0019]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described below in detail with reference to the embodiments shown in the drawings. This does not limit the present invention. FIG. 1 is a block diagram showing a configuration diagram of a living body inspection apparatus according to the present invention, in which a "blood vessel width measurement mode", a "blood component concentration measurement mode", and an "oxygenation rate measurement mode" can be selectively executed. In FIG. 1, a detection unit 1 includes a light source unit 11 for illuminating a part of a living body (here, a human finger) that fits a blood vessel, and a light image (here, a transmitted light image) of the illuminated living body part. A light receiving unit 12 for imaging is provided.

The analysis unit 3 includes a data processing unit 2, an output unit 24
When the light receiving unit 12 captures a part of the living body several times in time series, the data processing unit 2 (Here, the feature extraction unit 31 that extracts the coordinates of the depression in the contour of the first joint position of the finger), the storage unit 32 that stores the extracted features, the comparison unit 33 that compares the features, An analysis area setting unit is provided for setting an analysis area that matches the same blood vessel site in a plurality of images based on the result.

The data processing unit 2 extracts an image density distribution of a portion of the captured image that linearly crosses a blood vessel in the analysis area at right angles as an image density profile, and an extracted unit 21. A quantification unit 22 for quantifying the morphological characteristics of the concentration profile; a calculation unit 23 for calculating the blood vessel diameter, blood component concentration, oxygenation rate, etc. based on the quantified characteristics; and a storage unit for storing the calculation results 25.

Further, the analysis unit 3 includes an output unit (liquid crystal monitor) 24 for outputting a calculation result and a monitor image, and an operation unit 35.
(Keyboard) for inputting measurement mode setting, initial setting of an analysis area, calculation conditions of the calculation unit 23, operator information and measurement data. The data processing unit 2 is constituted by a personal computer.

FIG. 2 is an external perspective view of the apparatus shown in FIG. 1 and shows a state where the detecting unit 1 is mounted on the mounting unit 4.
The detection unit 1 includes an arm 5 and a housing 6.
A light source unit 11 (lens and CCD) is built in the housing 6 facing the arm 5. A finger 16 is held between the arm 5 and the housing 6, the light is irradiated to the finger 16, and the transmitted light is received by the light receiving unit 12 as a transmitted image. Output unit (LCD monitor) 24
Is connected to the analysis unit 3 by a hinge 10 and can be folded. The analysis unit 3 has an insertion port 36 for an external storage medium, and can insert an external storage medium and record measurement information and the like.

FIG. 3 is a side view of the apparatus shown in FIG. 1 as viewed from the detection unit 1 side. The detection unit 1 mounted on the mounting unit 3 includes a connector 7 of the detection unit 1 and a connector of the analysis unit 3. 8 is directly connected. As described above, since the detection unit 1 and the analysis unit 3 are integrated with the mounting unit 4 via the connectors 7 and 8, it is convenient for carrying.

FIG. 4 shows a state in which the detecting section 1 is detached from the mounting section 4 of the analyzing section 3 and the detecting section 1 and the analyzing section 3 are connected by a connection cord with a connector. By removing the detection unit 1 from the mounting unit 4 of the analysis unit 3, the degree of freedom of measurement is expanded, and measurement in a free posture such as a sitting position or a lying position is enabled.

As described above, since the detection unit 1 can be freely attached to and detached from the analysis unit 3, it is easy to replace the detection unit 1 and flexibly cope with a change in the measurement target (for example, for adults or children). it can.

FIG. 5 shows an example of the operation unit 3 (keyboard). The operation unit 3 includes a “POWER” key for turning on the apparatus power, a “menu” key for highlighting a menu in a command area, an “input” key for executing a selected item of the menu and inputting measurement information or measurement data. , "Cancel" key to return to the menu tree or cancel input, "Cursor" to switch pages or move the cursor
It consists of a key, a "measurement" key for executing a measurement sequence, and a "number" key for inputting a number.

FIG. 13 is a front view of the light source unit 11 and LE.
It is composed of a light emitting element provided with D11a, LED11b and LED11c. The center wavelength is 830n as the LED 11a.
m, L3989 having a half width of 40 nm (manufactured by Hamamatsu Photonics Co., Ltd.) was used.
L25656 (manufactured by Ibid.) Having a half width of 50 nm is used as the LED 11c, and an LED (manufactured by Ibid.) Having a center wavelength of 660 nm and a half width of 40 nm is used as the LED 11c. In addition,
As described later, in the “blood vessel width measurement mode”, the LED 11
a is turned on, and in the “blood component concentration measurement mode”, L
The EDs 11a and 11b are set to L in the “oxygenation rate measurement mode”.
The EDs 11a, 11b and 11c are turned on.

The procedure for measuring the blood vessel width, blood component concentration and oxygenation rate performed in such a configuration will be described. (1) Blood vessel width measurement mode In this mode, a blood vessel image is captured a plurality of times in a time series using one wavelength. First, in FIG. 6, the “vessel width measurement mode” is set by operating the operation unit 35 (step S <b> 1), and when the finger 16 is illuminated and imaged by the LED 11 a (first wavelength), as shown in FIG. Together with the outline 16a of the finger 16, an image 41 is obtained that combines the blood vessel (vein) image 40 localized on the skin surface on the light receiving unit 12 side (step S).
2). Next, the analysis area A1 is set in the image 41 (step S3).

The procedure for setting the analysis area Al is executed according to the procedure shown in FIG. That is, when the measurement is performed for the first time (step S31), a region having the best contrast in the blood vessel image 40 is searched, and the determined region is set as the analysis region A1 (step S32). The analysis area A1
Is automatically set by the analysis area setting unit 34, but may be manually set by the user operating the operation unit 35 while watching the monitor image output to the output unit 24.

In the set analysis area A1, 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 extraction unit 31 extracts the joint position P1 from the depression of the outline 16a in the image 41, and stores the coordinates of the position P1 at which the sleeve is set 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. 9 is obtained in the previous step, the stored coordinates of the analysis area A1 are read out, and the joint position P2 is characterized from the image 41a. It is extracted by the extraction unit 31 (steps S36 and S37).

Next, the difference between the coordinates of the joint position P1 set at the time of the first measurement and the joint position P2 extracted this time is expressed by the following equation.
X and ΔY are calculated by the comparison unit 33 (step S
38). If neither △ X nor △ Y exceeds the predetermined allowable range δ (step S39), the analysis area setting unit 34 shifts the initially set analysis area A1 by △ X and △ Y, A new analysis area A2 is set (step S40).

Thus, the blood vessel part in the area A2 becomes substantially the same as the blood vessel part in the area A1 set at the time of the first measurement. In this way, even if the number of times of one finger of the subject is measured in time series (for example, every two hours), the analysis areas A1, A2,... Is measured. In step S39, if any of △ X and △ Y exceeds the allowable value δ, it is determined that the finger 16 is not properly set with respect to the detection unit 1 and an “error” is output to the output unit 24. Is displayed.

Next, in step S4 of FIG. 6, when the profile extraction unit 21 creates a density profile (FIG. 10) in the direction perpendicular to the blood vessel in the set analysis region, the quantification unit 22 Normalize the density profile with the 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. 10 is normalized as shown in FIG. 11 (step S5). By doing this,
A density profile that does not depend on the amount of incident light can be obtained.

The calculation unit 23 calculates the peak height h1 from the standardized density profile (FIG. 10), and calculates (1/1)
2) The distribution radiation (half-value radiation) w1 at h1 is calculated as the blood vessel width and stored in the storage unit 25 (step S6). When the measurement of the predetermined number of times is completed, a graph or a table representing the time-series change is created from the calculated blood vessel width and displayed (steps S7 to S9).

(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 in a time series. First, in FIG. 6, the “blood component concentration measurement mode” is set by operating the operation unit 35 (step S11), and the LED 11a (first wavelength) and L
The finger 16 is sequentially illuminated by the ED 11b (second wavelength), and images are taken (steps S12 and S13), respectively.
For the image obtained at the first wavelength, an analysis area is set according to the same procedure as step S3, that is, the procedure shown in FIG. 7 (step S14).

Next, the profile extracting section 21 creates a first density profile and a second density profile as shown in FIG. 10 for each image obtained by the first and second wavelengths (step). S15).
The quantification unit 22 normalizes each of the first and second concentration profiles with the baseline as shown in FIGS. 11 and 12 (step S16).

The calculation unit 23 calculates the peak height h1 and the half-value width w1 for each of the standardized density profiles (FIG. 11), and similarly calculates the peak for the standardized second density profile (FIG. 12). The height h2 is calculated (step S17), and the hemoglobin concentration HGB and the hematocrit HCT are calculated as follows (step S18).

That is, assuming that the scattering coefficient of blood at the first wavelength is S1, the absorption coefficient is A1, and Beer's law is approximately satisfied, log (1-h1) =-k (S1 + Al) 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 hemoglobin amount of 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 by the LED 11b (second wavelength) is similarly calculated as S2
= Σ2 · HCT, A2 = ε2 · HGB (σ2, ε2 are constants) log (1-h2) = − k (S2 + A2) · w1 = − (kσ2 · HCT + kε2 · HGB) · w1 (4) Since k, σl, σ2, ε1, ε2 are determined theoretically or experimentally, when h1, h2, w1 are obtained,
HGB and HCT are determined 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 that in the case where there is no tissue. 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 is maximized 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 calculation unit 23 creates and displays a graph or a table representing the time-series change from the calculated value (steps S19 and S20).

(3) Oxygenation Rate Measurement Mode In this mode, an operation of imaging once for each of a plurality of wavelengths is performed a plurality of times (in time series). The “oxygenation rate measurement mode” is set by the operation unit 35. Then, as shown in FIG. 14, the finger 1 is moved by the LED 11a (first wavelength: 830 nm).
6 is illuminated and imaging is performed (step S51). Next, LE
The finger 16 is illuminated with D11b (second wavelength: 890 nm), and an image is captured similarly (step 52). Next, LED
The finger 16 is illuminated with 11c (third wave: 660 nm) and imaged (step S53). Then, the analysis area is set according to the procedure shown in FIG. 7 (step 54).

Next, each density profile of the image at the first, second and third wavelengths is created as shown in FIG. 10 (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 a table representing the chronological change may be created and displayed (step S
59-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 ε1 for oxidized and reduced hemoglobin at the first wavelength (because of equal absorption) and the absorbance for oxidized and reduced hemoglobin at the second wavelength are ε2
(Because of equal absorption), the absorbances for the 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 concentration profile normalized for each wavelength is h1, h2, h3 and the width is w1, respectively, log (1-h1) = − k (A1 + S1) in the same manner as Expression (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 is considered to be proportional to the hematocrit HCT of blood similarly to S1 and S2, 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.

FIG. 15 shows an output unit 24 (liquid crystal display).
5 is a display example. There are a graph display area 51, a measurement data display area 52, a measurement information area 53, a message area 54, a data display format switching area 55, and a command area 56.
The graph display area 51 can display biological component information and optional information obtained from the measurement device as a graph of time-series data. The measurement data display area 52 can display measurement data at a certain measurement point on a graph. Measurement information area 53
Indicates the measurement information such as the measurement number, the measurement person's name, the date of birth, and the gender. The message area 54 can display a message indicating the state of the system or a message urging the measurer to operate. The data display format switching area 55 displays an icon for switching the data display format, and displays a graph,
The display can be switched to any of a list, an image, and the like. In the command area, icons for executing various commands are displayed. When each icon is selected, recording of measurement data to a PC card, deletion of a file, setting, data transfer, printing, maintenance, and the like can be executed.

The graph shown in the graph area 51 of FIG. 15 shows the blood vessel width, hemoglobin HGB, and oxygenation rate SVI obtained by measuring the same subject every day before exercise.
And a time series graph based on measurement data input by selecting a time trial time from arbitrary selection information. Although not shown in the graph area 51, lactic acid (lactic acid value), blood pressure H (maximum blood pressure value), and heart rate are selected and input as optional information, and are input using the "cursor" key shown in FIG. The display area can be switched to be displayed as a time series graph in the graph area 51. Also, use the "cursor" key to indicate the measurement points on the time-series data graph.
Can be moved, and the measurement date, the measurement time, the measurement result and the comment at that time are displayed in the graph area 51 in the data display area 5.
2 can be displayed.

As described above, the relation between the measurement result of the measuring device and the optional information can be understood at a glance in a time series, and the prediction (increase or decrease tendency) of the measurement result is easy and convenient. Further, the item reflecting the condition can be arbitrarily selected, and the condition can be managed according to the purpose.

[0056]

According to the present invention, the measurement results can be displayed as a graph or a table of the time-series data, or can be displayed in connection with arbitrary selection information. As a result, the measurement result and the condition are known in a time series, and the prediction (increase or decrease tendency) of the measurement result is easy and convenient. Further, the item reflecting the condition can be arbitrarily selected, and the condition can be managed according to the purpose. Such a non-invasive biological component measurement device can be carried anywhere, regardless of the measurement location, and it can easily and quickly measure hemoglobin concentration, which is useful as an aerobic exercise performance index that you want to measure regularly, and the measurement results Is also displayed as time series data, which has the advantage that the condition of the day can be seen at a glance.

[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 side view showing an outer shape of the embodiment of the present invention.

FIG. 4 is a perspective view showing an outer shape of the embodiment of the present invention.

FIG. 5 is a diagram showing an operation unit according to the embodiment of the present invention.

FIG. 6 is a flowchart showing the operation of the embodiment of the present invention.

FIG. 7 is a flowchart showing the operation of the embodiment of the present invention.

FIG. 8 is an explanatory diagram showing an example of an image obtained by the embodiment of the present invention.

FIG. 9 is an explanatory diagram showing an example of an image obtained by the embodiment of the present invention.

FIG. 10 is an explanatory diagram showing a density profile of an image example according to the embodiment of the present invention.

FIG. 11 is an explanatory diagram showing a normalized density profile according to the embodiment of the present invention.

FIG. 12 is an explanatory diagram showing a normalized density profile according to the embodiment of the present invention.

FIG. 13 is a front view of the light source according to the embodiment of the present invention.

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

FIG. 15 is an explanatory diagram showing a display example of the embodiment of the present invention.

[Explanation of symbols]

 Reference Signs List 1 detection unit 2 data processing unit 3 analysis unit 4 mounting unit 11 light source unit 12 light receiving unit 21 profile 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 Operation unit

 ──────────────────────────────────────────────────続 き Continued on the front page F term (reference) 2G059 AA01 BB04 BB12 CC18 EE01 EE11 GG01 GG02 KK04 MM01 MM10 4C038 KK00 KK01 KL07 KM00 KX01

Claims (4)

[Claims] A light source unit for supplying light to a living body to be inspected; a light receiving unit for detecting optical information on the living body receiving the light; a data processing unit for performing data processing on the optical information;
An output unit for outputting biological component information obtained by data processing, and an operating unit for inputting and operating data necessary for data processing, and the data processing unit is arbitrarily selected as biometric component information of the same person. A non-invasive biological component measurement device characterized by displaying time-series data of optional information as an analysis result on an output unit. 2. The non-invasive biological component measuring device according to claim 1, wherein the optional information is an action result of the same person. 3. The non-invasive biological component measuring device according to claim 2, wherein the optional information is the exercise performance of the same person. 4. The non-invasive biological component measuring apparatus according to claim 3, wherein the optional information is a time trial result of the same person.