JP2001013062A - Optical-image measuring apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To acquire significant information on a living body in a measurement by using information on an image obtained from a two-dimensional change amount without measuring an absolute amount and to diagnose the state of the tissue of the living body. SOLUTION: In this optical-image measuring apparatus, a living body (a specimen 10) is irradiated with light, light which is emitted from the living body is detected by a two-dimensional detector (an optical detection means 21), and an image is obtained. The optical-image measuring apparatus is constituted in such a way that it is provided with an image measuring means 2 which acquires image data at a plurality of wavelengths in a time-dependent manner and that it is provided with an image computing means 3 which computes an image used to find information on the living body by using a plurality of image data whose measuring wavelengths and measuring times are respectively different. The two-dimensional change amount of the specimen such as the living body or the like is acquired as image data in a plurality of times. The acquired image data at many wavelengths and in the plurality of times are computed. Significant information on the living body in a measurement is obtained. As a value which is related to the information on the living body, an oxyhemoglobin amount or a deoxyhemoglobin amount can be used.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical image measuring apparatus, and more particularly to an apparatus for measuring a temporal change of a component in each part of a living body, which can be applied to diagnosis of normal or abnormal tissue of a living body. About.

[0002]

2. Description of the Related Art There is known an optical measuring device which irradiates a subject such as a living body with light, receives light scattered, reflected and absorbed by the subject, and optically measures a tissue of the subject. .
Various techniques have been proposed for this optical measuring device. Hereinafter, examples of the related art of the optical measurement device will be listed.

[0003] By irradiating a living body or the like with light having a wavelength from visible light to near-infrared light and absorbing or scattering inside the living body, the light coming out of the living body is received and the absorption spectrum of the detected light is measured. 2. Description of the Related Art A biological monitor for examining and diagnosing a tissue of a living body is known. An oxygen monitor is known as this biological monitor. Oxygen monitor is oxygenated hemoglobin (oxyhemoglobin) combined with oxygen
The relative change and absolute amount of oxygenated hemoglobin and deoxygenated hemoglobin are measured non-invasively using the difference in spectrum between deoxygenated hemoglobin and deoxygenated hemoglobin separated from oxygen.

In general, in a biological measurement, a reference substance having other optical characteristics having the same characteristics as that of a living body cannot be obtained even if the content concentration is known or zero concentration, so that a relative change from a value at a specific time is obtained. Is relatively easy to obtain, but the absolute value is difficult to measure. Therefore, there has been proposed a method of measuring the absolute amount using the outputs of a plurality of detectors at different distances from the light source on the assumption that the composition is uniform.

[0005] There have been proposed two-dimensional detectors and those that obtain an image output or an output similar to an image by arranging a plurality of two-dimensional detectors. It is also known that at a measurement depth measured by an optical measurement device, the measurement depth measured by reflection measurement depends on the wavelength and the distance between the light transmitting point and the light receiving point.

[0006]

In an optical measuring device, it is sometimes required to diagnose the state of blood vessels and blood flow in a shallow part of a living body such as skin. In order to determine whether blood vessels and blood flow in such a shallow part of a living body are normal, two-dimensional information of the absolute amount at the time of the measurement is necessary in a part where the measurement depth is shallow.

However, in the above-described optical measuring apparatus, in a method of simply detecting reflected light or transmitted light from a subject with a two-dimensional detector to obtain a two-dimensional image, the measured value is a relative value. Since the reference value cannot be obtained, the obtained image is not meaningful for diagnosing the state of blood vessels or blood flow.

[0008] Further, using the method for measuring the absolute amount described above, 2
In order to obtain dimensional information, it is necessary to arrange multiple detectors at different distances from the light source, and to calculate the absolute amount for each detector, which makes the device complicated and increases the operation time. Problem arises. In addition, in the absolute amount measurement described above, since the composition is assumed to be uniform, if the composition is non-uniform, the measured value is not significant, and an accurate diagnosis cannot be performed. There are also problems.

Therefore, the present invention solves the above-mentioned conventional problems, and obtains significant biological information at the time of measurement using image information obtained from a two-dimensional change amount without performing absolute amount measurement. It is an object of the present invention to provide an optical measuring device capable of diagnosing a tissue state of a living body.

[0010]

According to the present invention, a plurality of image data is obtained by measuring a two-dimensional change amount of a subject such as a living body by changing a measurement wavelength and a measurement time, and obtaining a plurality of image data. By calculating image data at a plurality of times, significant biological information at the time of measurement is obtained, and this is used for diagnosis of a tissue state of a living body such as a blood vessel state or a blood flow state. The biological information may be information on a stenosis state such as a thinned or clogged blood vessel of a patient.

An optical image measuring apparatus according to the present invention is an optical image measuring apparatus which irradiates a living body with light and detects light emitted from the living body with a two-dimensional detector to obtain an image. A plurality of image data having different measurement wavelengths and measurement times, and an image calculation means for performing image calculation for obtaining biological information at a specific time. The two-dimensional change amount of the subject, such as, acquired as a plurality of image data with different measurement wavelength and measurement time, acquired multi-wavelength,
By calculating image data at a plurality of times, significant biological information at the time of measurement is obtained.

The value of the measurement wavelength of the image data obtained by the image measuring means and the number of the measurement wavelengths can be determined according to the biological information to be obtained. Further, the content of the image calculation performed by the image calculation means can be determined by a calculation formula determined according to the data type and the number of data of the image data obtained by the image measurement means and the desired biological information.

FIG. 1 is a diagram for explaining a schematic configuration of an optical image measuring device according to the present invention. In FIG. 1, an optical image measuring device 1 includes an image measuring means 2, an image calculating means 3, and an image display processing means 4 for displaying an obtained image. Further, a blood flow change inducing means 5 for inducing a change in the blood flow state of the living body and changing the light emitted from the living body can be provided.

The image measuring means 2 detects light emitted from the subject 10 by irradiation with the light source 11 with a two-dimensional detector or the like, and outputs image data of a plurality of wavelengths (wavelengths λ1 to λn). The image processing apparatus includes a detecting unit 20 and an image data obtaining unit 27 that obtains the image data in time series. The image data acquisition means 27 converts the image data D1 (t1), D2 (t1),.
, T2,... Are obtained as time-series image data, and the image calculation means 3 performs a calculation process using the time-series image data.

Here, the image data D1 (t1), D2
(T2),... Represent not a single numerical value but a representative pixel matrix. For example, in the case of a 100 × 100 image of 10,000 pixels, D1 (t1) is originally 10
It has an amount of 10,000 total pixels represented by a matrix of 0 rows × 100 rows. Here, in order to simplify the notation, one of the pixels is represented as D1 (t1). Therefore, when D1 (t1) appears during the calculation,
It means that the same numerical value has the total number of pixels of the matrix.

The operations f, g, and h are examples of image operations performed by the image operation means 3, and a plurality of image data having different measurement times for a plurality of wavelengths from time-series image data provided in the image data acquisition means 27. Is typically used to calculate the temporal change rate of the image, and the biological information is obtained based on the calculation. For example, the operations f, g, and h are the wavelengths λ
.. Λm are calculated using the image data at times ta, tb, and tc as variables.

As a set of three times (ta, tb, tc), for example, (t1, t2, t3) first, (t2, t3, t4), (t3, t4, t5) Then, at the time shifted sequentially, the image calculation defined by f, g, and h is performed.

For example, when the oxyhemoglobin (oxygenated hemoglobin) variation and the deoxyhemoglobin (deoxygenated hemoglobin) variation in the living body are acquired as basic quantities related to biological information, the image measuring means 2 has two wavelengths. The image data is measured over time. The image calculation means 3
As shown in the following formulas (1), (2), and (3), an operation of multiplying each value of four image data obtained from the image data of two wavelengths at two times by a predetermined weight, and adding or subtracting these values. The process is performed to determine the oxyhemoglobin variation and the deoxyhemoglobin variation.

[ΔOxyHb], [ΔdeOxyHb] [ΔOxyHb] = k1 × D1 (t2) + k2 × D2 (t2) −k1 × D1 (t1) −k2 × D2 (t1) [ΔdeOxyHb] = k3 × D1 (t2) + k4 × D2 (t2) −k3 × D1 (t1) −k4 × D2 (t1) (1) [ΔOxyHb], [ΔdeOxyHb] [ΔOxyHb] = k1 × D1 at the second time point (T3) + k2 × D2 (t3) −k1 × D1 (t2) −k2 × D2 (t2) [ΔdeOxyHb] = k3 × D1 (t3) + k4 × D2 (t3) −k3 × D1 (t2) −k4 × D2 (t2) (2) [ΔOxyHb], [ΔdeOxyHb] [ΔOxyHb] = k1 × D1 (t4) + k2 × D2 (t4) −k1 × D1 (t3) −k2 × D2 ( t3) [ΔdeOxyHb] = k3 × D1 (t4) + k4 × D2 (t4) −k3 × D1 (t3) −k4 × D2 (t3) (3) where D1 (t) is at time t of wavelength λ1. A value representing one pixel of image data is shown, and D2 (t) is a wavelength λ2
3 shows a value representing one pixel of the image data at time t.

In the above equations (1), (2) and (3),
[ΔOxyHb] is the pixel value of the variation of oxyhemoglobin, and [ΔdeOxyHb] is the pixel value of the variation of deoxyhemoglobin. The value of [[Delta] OxyHb] at the first time point is four pixel values D1 obtained from a total of four measurement images of two wavelengths at time points t1 and t2 as in equation (1).
(T1), D2 (t1), D1 (t2), D2 (t2)
Is multiplied by (−k1, −k2, k1, k2) as a weight, and is added. The value of [ΔdeOxyHb] at the first time point is the same as the original pixel value D1.
(T1), D2 (t1), D1 (t2), D2 (t2)
Are multiplied by (−k3, −k4, k3, k4) as weights and added.

As shown in equations (2) and (3), the values at the second and third points in time are shifted from time (t1, t2) to (t2, t3), (t3, t4), respectively. Can be obtained by: Note that the original pixel value D1
(T1), D2 (t1), and the like can be obtained from the output value of the two-dimensional detector or a value obtained by logarithmically converting the detector output.

Since the above calculation is performed for each pixel, the obtained image is an image in which the variation amount of oxyhemoglobin or deoxyhemoglobin is set to each pixel. One aspect of the processing performed by the image calculation means is an image of the temporal change rate of the biological information at a specific time using the above-described image data. In this case, the image of the rate of change over time can be obtained by an operation for obtaining a differential value of image data or an operation for obtaining a difference between image data at adjacent times.

In another aspect of the processing performed by the image calculation means, the difference in time at which the rate of change of the image data of different wavelengths is maximum is imaged. That is, the value of the phase delay is imaged. For example, it has been found that in places where vascular occlusion or the like exists in the blood vessel distribution, changes in oxyhemoglobin are delayed more than in other normal places. Therefore, by detecting the phase change, a biological condition such as vascular occlusion can be diagnosed.

In another mode of processing performed by the image calculation means,
The maximum value of the amplitude of the data value of each image constituting the image data or the maximum value of the differential value amplitude in each image is obtained, and the maximum value is used to standardize the amplitude value or the differential value amplitude of each image. An image is formed using the converted values.
As a result, a change in a pixel having a small amplitude can be detected without overlooking it.

The blood flow change inducing means is a means for inducing a change in the blood flow state of the living body, and includes a cuff wound around the arm to stop the blood flow, a heater for increasing the skin temperature, and ice or the like for lowering the skin temperature. Cooling means, devices that provide light electrical stimulation to the nerves, etc., can be used, which allow squeezing and release by the cuff, temperature, pressure, electricity, light irradiation on the skin,
Stimulation such as application of a drug, administration of a drug, and the like can be applied.

The inventor squeezes the upstream side of the examination site with a cuff or the like to intentionally stop and release the blood flow, thereby causing a rapid change in the blood flow in the blood vessel. ,
An experiment and a study were conducted in which a change in the amount of oxygenated hemoglobin in the skin was displayed as an image using the optical image measurement device of the present invention. As a result, a change in the amount of oxygenated hemoglobin could be recognized depending on the presence or absence of the change, the magnitude of the change, and the change pattern of the response speed of the change depending on the skin portion. The pattern of this change is related to the distribution of blood vessels that supply oxygen to the skin.When an occlusion is created in a blood vessel, the blood flow decreases, and the amplitude of the change in oxygenated hemoglobin in the occlusion on the image is reduced. It has been found that even significant suppression is achieved.

The blood flow change inducing means intentionally changes the blood flow of the living tissue, detects the change in the blood flow state as image data by the optical image measuring device, and calculates an image relating to the biological information from the image data. Ask for it. An abnormality in a blood vessel of a living tissue can be determined from the obtained change pattern.

According to another aspect of the present invention, an outer shape image is formed based on one image data of a plurality of wavelength image data measured by the optical image measuring device of the present invention, and the multi-wavelength, plural The image obtained from the image data at the time is displayed in a superimposed manner. This display has an effect that the position of the biological information can be easily confirmed. In this case, since only one of the original multi-wavelength images is used for the outline image, no extra hardware device is required, and there is a great advantage that the outline image and the functional image can be superimposed.

According to the optical image measurement device of the present invention, the activity distribution of oxygen supply in each part of the living tissue can be displayed as an image, and an abnormality such as occlusion of a blood vessel can be determined from the pattern. ADVANTAGE OF THE INVENTION According to the optical image measuring device of this invention, since an X-ray and a contrast agent are not required, the influence on a living body can be reduced and it can be set as a measuring device suitable for repeated measurement in judgment of a therapeutic effect, etc. . According to the optical image measurement device of the present invention, since two-dimensional image data can be obtained by applying a two-dimensional detector, a large number of light transmitting and receiving devices are not required, and the device can be downsized. In addition, the cost of the apparatus can be reduced, and the cost of the test can be reduced because no reagent is required for the measurement.

[0030]

Embodiments of the present invention will be described below in detail with reference to the drawings. The optical image measuring device 1 of the present invention can be configured according to FIG. Less than,
An example of the configuration of the light detecting means 20 will be described with reference to FIGS. 2 and 3, and an example of the calculation of the image calculating means 3 will be described with reference to FIGS.

FIGS. 2 and 3 show an example of the configuration of a light detecting means for measuring two wavelengths. FIG. 2 shows an example of a configuration using a plurality of optical systems, and FIG. 3 shows an example of a configuration for switching a single optical system. It is. In the first configuration example shown in FIG.
Is a lens system 21a, 21b for branching the light emitted from the subject 10 into two optical paths, and a CCD system for connecting the two branched optical paths.
A lens system 22 for guiding to the camera 25 side;
A first wavelength filter 23a and a second wavelength filter 23b are provided to separate the first wavelength component and the second wavelength component from the light of the two optical paths.

The intermediate images 24a and 24b of the respective wavelength components taken out by the first wavelength filter 23a and the second wavelength filter 23b are converted by the CCD camera 25 into the first images 24a and 24b.
The light is received by the light receiving unit 26a having the wavelength and the light receiving unit 26b having the second wavelength. Each of the light receiving units 26a and 26b can be configured by a two-dimensional detector, and acquires image data based on the light intensity detected for each pixel.

In the second configuration example shown in FIG. 3, the light detection means 20 includes one system of lens systems 21 and 22 for guiding the emitted light from the subject 10 and the first and second wavelength components. A first wavelength filter 23a, a second wavelength filter 23b, and a CCD camera 25 are provided to separate the first wavelength filter 23a and the second wavelength filter 23, respectively.
b can be independently introduced into the optical path.

FIG. 3A shows a first wavelength filter 23a.
Is shown on the optical path, and FIG. 3B shows a case where the second wavelength filter 23b is introduced on the optical path. Each intermediate image 24a of each wavelength component extracted by the first wavelength filter 23a or the second wavelength filter 23b
(FIG. 3A) and the intermediate image 24b (FIG. 3A)
The light is received by the light receiving unit 26 on the D camera 25. The light receiving unit 26 is configured by a two-dimensional detector, and acquires image data based on light intensity detected for each pixel. The first wavelength filter 23a and the second wavelength filter 23b can be introduced by being alternately moved on the optical path.

FIGS. 4 and 5 are diagrams for explaining image calculation when measuring at two wavelengths. Set the measurement time to t1,
When t2, t3, t4, t5,...
.., G1, G2, G3, G4, G5,..., And the signal value at each time of each pixel of the image data based on the wavelength component of wavelength λr. R1, R2, R3, R4, R
5, and so on.

The signal value of each pixel is representative of each pixel of the CCD. For example, in a 512 × 600 CCD, each of 300,000 pixels has a signal value corresponding to a received light image. Will be. The signal value Gi of the pixel at the wavelength λg and the signal value Ri of the pixel at the wavelength λr
Is 0 ≦ Gi, R for a 12-bit signal.
i is an integer within the range of 4095 (= 2 ^{1 2} );
When the values of i and Ri are small, it indicates that the light intensity is weak,
When the values of Gi and Ri are large, it indicates that the light intensity is high.

To obtain the processed image, the image data Gi of the first wavelength λg and the image data Ri of the second wavelength λr at the time i, and the image data Gj and the second data of the first wavelength λg at the time j are obtained. An operation is performed using a combination of four image data having different measurement wavelengths and measurement times from the image data Rj of the wavelength λr, and a set of image data is obtained by this operation. Note that time i and time j are different times. For example, when time i is a certain measurement time, time j can be the next measurement time.

FIG. 4 schematically shows the relationship between measured image data and processed image data. In FIG. 4, at time t
1 and the signal value G at time t2.
2, R2 (combination of four measurement image data surrounded by a solid line in the figure) is used to perform processing such as the above-described calculation formula (1) to obtain processed image data D12.
Next, the same arithmetic processing is performed by using the signal values G2 and R2 at time t2 and the signal values G3 and R3 at time t3 (combination of four measurement image data surrounded by a broken line in the drawing). The processing image data D23 is obtained. Hereinafter, similarly, the calculation is performed using the combination of the measurement image data having different wavelengths and times, and the processed image data D34,
D45,...

575 nm (green) as the first wavelength λg
By using 600 nm (red) as the second wavelength λr, changes in oxyhemoglobin and deoxyhemoglobin can be obtained from the image data Gi and Ri.

The amount of change in oxyhemoglobin [ΔOxyHb
] And the amount of change in deoxyhemoglobin [ΔdeOxyHb]
Are represented by the following equations using image data Gi, Gj, Ri, Rj, respectively. [ΔOxyHb] = k1 (logGj−logGi) + k2 (logRj−logRi) (4) [ΔdeOxyHb] = k3 (logGj−logGi) + k4 (logRj−logRi) (5) where k1 to k4 are oxyhemoglobin It is a coefficient obtained from the spectrum of deoxyhemoglobin,
For example, k1 = −79, k2 = 212, k3 = 20, k4 =
-322 or the like.

FIG. 5 is a diagram conceptually showing the processing operation.
FIG. 5 conceptually illustrates a processing operation for obtaining image data relating to a living body from a measured image data change rate, as in the case of performing the above-described calculation of the amount of change in oxyhemoglobin and deoxyhemoglobin using a combination of four measurement image data. Is shown.

FIG. 5A shows the time (t1, t2, t3, t4, t4) of each pixel D1 (λg) of the image at the first wavelength.
t5, t6,...), and FIG. 5B shows each time (t) of each pixel D2 (λr) of the image at the second wavelength.
1, t2, t3, t4, t5, t6,...). FIG. 5C shows the values at each time (t2, t3, t4, t5, t6,...) Of each pixel of the image obtained by the calculation.

In this case, the value at the time corresponding to the time t2 in FIG. 5C is three data (data at the times t1, t2, and t3) enclosed by broken lines in FIG.
In FIG. 5B, three data (time t
1, data at t2, and t3).

Similarly, the value at the time corresponding to time t3 in FIG. 5 (c) is a total of six data at times t2, t3, and t4 enclosed in FIGS. 5 (a) and 5 (b). Is obtained. In the following, the image sequence corresponding to the change rate can be obtained by performing the calculation while shifting one step at a time in the same manner as in. Next, in the optical image measurement device according to the present invention, the arithmetic expression (4),
FIGS. 6 and 7 show examples in which the amount of change in oxyhemoglobin and the amount of change in deoxyhemoglobin were determined using (5).

In FIG. 6, the amount of change in oxyhemoglobin is indicated by a broken line, and the amount of change in deoxyhemoglobin is indicated by a solid line. FIG. 6 shows the amounts of change in oxyhemoglobin and deoxyhemoglobin at two points (points A and B in FIG. 7) of the same subject with the initial value being 0. FIG. 6A shows the amount of change at point A, and FIG.
(B) shows the amount of change at point B.

In FIG. 6, time point 1 is a value before the arm portion of the subject is tied by the cuff, time point 2 is a value 2 minutes after the cuff is started to be tied, and the cuff is released after this time point. . From the change in oxyhemoglobin (dashed line) and the change in deoxyhemoglobin (solid line) in FIG.
It is observed that the sample is in the most deoxidized state, rapidly returns to the direction of oxygenation by releasing the cuff, and a gradual change from time 3 to time 7 is observed. In section a in FIG. 6 (section between time 1 and time 2), deoxyhemoglobin greatly increases and oxyhemoglobin largely decreases. In section b (section between time 2 and time 3),
Rapidly returns to oxygen.

The change at the point A shown in FIG.
By comparing with the change at the point B shown in FIG. 6B, it is possible to observe the difference depending on the part of the subject.
FIG. 7 is an image showing a difference between oxyhemoglobin changes in each of the sections a and b in FIG. FIG.
7A is a two-dimensional distribution image of oxyhemoglobin in the section a, and FIG. 7B is a two-dimensional distribution image of oxyhemoglobin in the section b. In FIG. 7A, the amount of oxyhemoglobin decreases as a whole, and in FIG. 7B, it increases conversely. However, the difference between locations is more remarkable. At point A, which is a typical comparison point, the range of increase / decrease of oxyhemoglobin is large, and at point B, the range of increase / decrease of oxyhemoglobin is small, and FIG.
Indicates that the amount of oxyhemoglobin increases at the point A and the change of oxyhemoglobin at the point B is small. Therefore, when the subject is stimulated, it is presumed that the blood flow greatly changes at the point A and the blood flow changes little at the point B, and the oxygen supply activity of each part of the living tissue is estimated. The degree distribution can be displayed as an image, and an abnormality such as occlusion of a blood vessel can be determined from the pattern.

In general, when the blood flow is slow, the amplitude of the variation of the measured value is small, so that it is difficult to see the change when an image is formed. Therefore, by storing a series of time-varying image data and performing normalization such as dividing the value at each time by the maximum value of the pixels in all image data, when the absolute value of the amplitude value is small, Can also perform good imaging.

In order to remove noise, a fixed threshold value is provided for a pixel having a small change amount with respect to the maximum amplitude, and the maximum value of the signal of the pixel does not exceed the threshold value. In such a case, normalization is performed using a certain threshold value instead of the maximum value. As a result, it is possible to prevent the image from deteriorating due to noise, and it is easy to extract a portion where the phase changes with a delay.

Further, according to the present invention, a contour image of the subject can be obtained using the output of one of the multiple wavelengths of the two-dimensional detector, and a blood flow change image or the like is included in the contour image. By superimposing and displaying, it is possible to easily confirm the part of the blood flow change. For example, it is possible to superimpose and display the outline image based on the black and white shading image and the increase / decrease of the oxygen state based on the pseudo color.

Normally, a plurality of images obtained by different measurements are displayed in a superimposed manner. However, in the present invention, different wavelengths are selected by the same apparatus to obtain images of different purposes, and furthermore, superimposed. Can be displayed.
As the outer shape image, an image of the outer shape with the filter removed may be used, or an image obtained with the filter attached may be used.

[0052]

As described above, significant biological information at the time of measurement is obtained by using image information obtained from a two-dimensional change amount without measuring the absolute amount, and the tissue state of the living body is measured. Can be diagnosed.

[Brief description of the drawings]

FIG. 1 is a diagram for explaining a schematic configuration of an optical image measurement device of the present invention.

FIG. 2 is a configuration example of a light detecting unit using a plurality of optical systems when measuring two wavelengths.

FIG. 3 is a configuration example diagram for switching a single optical system when measuring two wavelengths.

FIG. 4 is a diagram schematically showing a relationship between measured image data and processed image data.

FIG. 5 is a diagram conceptually showing a processing operation.

FIG. 6 is a diagram showing a change amount of oxyhemoglobin and a change amount of deoxyhemoglobin.

FIG. 7 is a diagram showing a two-dimensional distribution of a change amount of oxyhemoglobin and a change amount of deoxyhemoglobin.

[Explanation of symbols]

DESCRIPTION OF SYMBOLS 1 ... Optical image measuring device, 2 ... Image measuring means, 3 ... Image calculating means, 4 ... Image display processing means, 5 ... Blood flow change inducing means,
11 light source, 21 light detection means, 21a, 21b, 22
... Lens system, 23a, 23b ... Filter, 24a, 2
4b: Intermediate image, 25: CCD, 26, 26a, 26b: Light receiving unit, 27: Image data acquisition means.

Continuation of front page (72) Inventor Ikuo Konishi 1-term, Kuwabaracho, Nishinokyo, Nakagyo-ku, Kyoto-shi F-term in Shimadzu Corporation (reference) 2G059 BB12 BB13 CC18 EE11 FF01 JJ02 KK04 MM01 MM10 4C038 KK01 KL07 KX02

Claims (5)

[Claims] 1. An optical image measuring apparatus for irradiating a living body with light and detecting light emitted from the living body with a two-dimensional detector to obtain an image, wherein an image for measuring image data of a plurality of wavelengths over time is obtained. An optical image measurement device comprising: a measurement unit; and an image calculation unit that performs image calculation for obtaining biological information using a plurality of image data having different measurement wavelengths and measurement times. 2. The image measuring means measures image data of at least two wavelengths, and the image calculating means multiplies each pixel data of at least four images obtained from the image data of at least two times by a predetermined weight. The optical image measurement device according to claim 1, further comprising an operation of adding each image to obtain a value related to biological information. 3. The amount related to biological information is an amount of oxyhemoglobin or an amount of deoxyhemoglobin.
The optical image measurement device as described in the above. 4. The image calculating means calculates a differential image of time or a difference between images obtained between adjacent measurement times.
2. The apparatus according to claim 1, further comprising: means for calculating a time-varying image.
The optical image measurement device as described in the above. 5. An inducing means for inducing a change in the state of a living body and changing light emitted from the living body.
The optical image measurement device according to 3, or 4.