JP2000083931A - Apparatus for noninvasive vital inspection - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an apparatus for noninvasive vital inspection which is provided with a loading section to be loaded with a detecting section in an analyzing section and is so formed as to allow the free attachment and detachment of the detecting section and the analyzing section. SOLUTION: This apparatus for noninvasive vital inspection comprises the detecting section 1 and the analyzing section 3. The detecting section 1 has a light source section 11 for supplying light to the living body to be inspected and a photodetecting section 2 for detecting optical information from the living body which receives light. The analyzing section 3 has a data processing section for executing the data processing of the optical information from the detecting section 1, an output section 24 for outputting the information subjected to the data processing and a manipulating section 35 for inputting and manipulating the data necessary for the data processing. The analyzing section 3 has the loading section to be loaded with the detecting section 1.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

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

[0002]

2. Description of the Related Art A blood test is one of the most important tests in clinical tests and is frequently performed in hospitals and the like. As a device for performing this blood test, the number and size of red blood cells, white blood cells, and platelets that are blood cell components of blood obtained by blood collection, the hemoglobin concentration contained in red blood cells, hematocrit, and the like are quickly and automatically measured. Blood analyzers are commonly used.

However, such a device weighs several tens of kilograms even in a small device, and requires reagents such as a diluent and a hemolytic agent. Therefore, the patient must go directly to the laboratory, or the blood collected in the hospital room or the like must be transported to the laboratory in some form, and it is necessary to go to the hospital even for frequent tests such as anemia tests. there were. Also, these tests are currently performed by blood collection,
Frequent blood sampling not only burdens the patient, but also may cause an infection accident due to erroneous injection of a needle.

[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). Such a non-invasive biopsy device does not require a reagent, is small in size, can be carried around, and can be easily measured anywhere.

[Problems to be solved by the invention]

[0005] In the conventional non-invasive biopsy device, the detection unit and the analysis unit are separate or the detection unit and the analysis unit are integrated. In the former case, there is no problem with either of the above configurations when the detection unit is small, but when the detection unit is large, both need to be carried separately, which is inconvenient. Conversely, in the latter case, if the detection unit is integrally configured, the degree of freedom of measurement is reduced, that is, there is a possibility that a problem occurs in measurement in a free posture such as a sitting position or a lying position. Also change the measurement target (for example, for adults or children)
There is a problem that cannot be handled flexibly.

The present invention has been made in view of such circumstances, and has a non-invasive configuration in which a mounting section for mounting a detection section on an analysis section is provided so that the detection section and the analysis section can be freely attached and detached. An object of the present invention is to provide a living body inspection apparatus.

[0007]

The present invention comprises a detecting section and an analyzing section. The detection unit includes a light source unit for supplying light to a living body to be inspected, and a light receiving unit for detecting optical information from the living body that has received the light. The analysis unit includes a data processing unit that performs data processing on optical information from the detection unit, an output unit that outputs the information obtained by the data processing, and an operation unit that inputs and operates data necessary for data processing. . The analysis unit further includes a placement unit on which the detection unit is placed.

[0008] Further, the detecting section may be directly connected to the connector of the detecting section mounted on the mounting section of the analyzing section and the connector of the analyzing section, or may be connected via a connection cord to the connector of the detecting section and the connector of the analyzing section. A non-invasive biopsy device characterized in that the connections are made is preferred.

[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 detection section can be mounted on the mounting section of the analysis section, so that the detection section and the analysis section can be integrated, and the measurement section can be easily carried by one person. Handling becomes possible, for example. Further, since the detection unit and the analysis unit are directly connected by the connector, the connector can also serve as the electric signal port and the fixing unit, and the number of parts and cost can be reduced. In addition, since the device is used by being lowered from the mounting portion as needed, the degree of freedom of measurement is expanded, and the subject can be separated from the subject and can be measured in a free posture such as a sitting position or a lying position. In addition, replacement of the detection unit is facilitated, and it is possible to flexibly cope with a change in the measurement target (for example, for adults or children). Such a non-invasive biopsy device can be carried anywhere, regardless of the measurement location, can easily perform anemia tests that need to be performed frequently, easily and in a short time, the measurement results are displayed as time-series data, and the condition of the day is displayed. There are advantages 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

Claims (3)

[Claims] 1. A detection unit comprising: a light source unit for supplying light to a living body to be inspected; a light receiving unit for detecting optical information from the living body receiving the light; A data processing unit for performing data processing, an output unit for outputting data processed information, and an analysis unit including an operation unit for inputting and operating data necessary for the data processing; An apparatus for non-invasive living body examination, further comprising a placement section on which a detection section is placed. 2. The non-invasive biopsy according to claim 1, wherein the detection unit is directly connected to the connector of the detection unit and the connector of the analysis unit when the detection unit is mounted on the mounting unit of the analysis unit. Equipment. 3. The non-invasive biopsy device according to claim 1, wherein the detection unit is connected between the connector of the detection unit and the connector of the analysis unit via a connection cord.