JPWO2008010604A1 - Angiography apparatus and blood vessel distribution analysis system - Google Patents

Abstract

The purpose is to non-invasively and easily observe and photograph the vascular distribution of veins. An irradiating unit that can irradiate probe light toward the inspection target region and an imaging unit that receives scattered light and / or transmitted light from the inspection target region irradiated with the probe light, and the probe light emitted from the irradiating unit is an imaging unit An angiographic apparatus, a diagnostic apparatus for analyzing the imaging result, and an analysis system for the angiographic apparatus are provided so as not to be directly incident on the imaging apparatus.

Description

  The present invention relates to a device that irradiates a target region including a blood vessel with probe light and images the distribution state of the blood vessel, and based on the imaging result, the blood vessel distribution, the presence / absence of an abnormal region of angiogenesis, and / or the progress of the abnormality. Diagnosis devices, especially devices that irradiate the skin with near-infrared light and image the distribution state of blood vessels, and obtain information on the thickness and distribution of blood vessels from the imaging results to determine the presence or absence of tumors (eg, breast cancer) and others The present invention relates to an analysis system for discriminating the state of tissue inflammation or disease.

In recent years, breast cancer has been a leading cause of death among women, and efforts have been focused on early detection.
As a general examination for breast cancer, a doctor palpates the breast first. When an abnormal lump is found by palpation, it is confirmed by mammography (mammography) or ultrasonography (echography) whether tissue deformation due to a lesion is observed at a suspicious location. If any abnormalities are found by these examinations, the living tissue is further examined (such as breast duct photography, tumor marker examination, fine needle aspiration cytology), and a final diagnosis is performed.
Recently, breast cancer testing is encouraged for women older than a certain age, but the rate of regular checkups is not necessarily high for various reasons such as time constraints. For this reason, for early detection of breast cancer, it is important that the patient regularly conducts self-examination of the breast and finds an abnormality at an early stage. However, it is difficult to discriminate the presence or absence of a lump sufficiently by palpation by amateurs, and there are cases in which abnormalities are overlooked and potential tumors that cannot be found by palpation in the first place, so a more reliable self-examination method is required.
On the other hand, a method for detecting blood vessels in a living body by irradiating skin with near-infrared light having a wavelength of 700 to 900 nm, which easily penetrates living tissue, is a diagnosis of cardiovascular function, measurement of blood volume or blood pressure, or biometric authentication. Etc. are used.
For example, Japanese Patent Laid-Open No. 8-164124 (Patent Document 1) irradiates near infrared light on a finger, the back of a hand, etc., and an image sensor such as a CCD (Charge Coupled Device) is arranged on the back side of the inside of the body. A method for observing the spatial distribution of the intensity of transmitted light is described. Near-infrared light is obtained as a dark image in which the blood vessel portion is light-absorbed because the absorption coefficient by components constituting the human body is small but the absorption by hemoglobin is large.
However, derivation of a blood vessel image using near-infrared transmitted light can be used only in a relatively thin portion such as a finger or the back of a hand. In view of this, there has also been proposed a method for obtaining a blood vessel image by irradiating a human body with light and capturing the light reflected after entering the human body with an imaging device (for example, Japanese Patent Application Laid-Open No. 8-164125). ).
When reflected light is used, it is necessary to capture only light including blood vessel information (light that has been reflected after entering the human body). However, in general, the reflected light intensity on the skin surface is overwhelmingly larger than the reflected light intensity from the inside of the human body, so the latter needs to be suppressed in some way. For example, in JP-A-8-164125 (Patent Document 1), a liquid is applied to the skin surface to directly reduce the reflected light.
JP-A-8-164123 (Patent Document 2) irradiates skin with two types of light having different wavelengths of 400 to 600 nm and 600 to 800 nm, and the internal reflected light component is compared with the former in the former. There is described a method for obtaining a blood vessel image by subtracting images obtained by both methods using the small amount.
As described above, when a blood vessel image is obtained using light, the applicable part is limited in the transmission method, and can be used only in a limited part particularly in a breast cancer occurrence part. In addition, when the reflection method is used, it requires complicated work such as applying a liquid to the skin surface in order to suppress the reflected light from the skin surface, or a plurality of light sources, filters, dichroic mirrors, images There is a problem in that an expensive and complicated device including an analysis mechanism is required.
In addition to the above, for example, Japanese Patent Application Laid-Open No. 2005-21380 (Patent Document 3) and Japanese Patent Application Laid-Open No. 2005-218684 (Patent Document 4) irradiate a subject with light containing a specific wavelength component, and the light energy thereof. An invention relating to a biological information video apparatus that visualizes biological function information of a subject from an acoustic signal generated based on the above is described. This photoacoustic spectroscopic analysis method is used to identify glucose, hemoglobin, etc. contained in blood in a subject when the subject is irradiated with visible light, near infrared light, or mid-infrared light having a predetermined wavelength. An acoustic wave generated as a result of the substance absorbing the energy of the irradiation light is detected, and the concentration of the specific substance is quantitatively measured. Thereby, the distribution of blood vessels in the tissue can be determined, abnormal angiogenesis in the tissue region can be determined, and the position of a potential tumor can be known. Japanese Patent Application Publication No. 2004-525684 (Patent Document 5) describes an apparatus including an applicator for breast cancer examination that examines a tumor site using a fluorescence contrast method. Further, Japanese Patent Laid-Open No. 2002-272745 (Patent Document 6) discloses that a translucent member is pressed against a breast of a subject, and a ring-shaped irradiation unit is provided at the base of the breast so as to photograph through the pressing member. A method is described.
However, the photoacoustic spectroscopic analysis method is also complicated and expensive. In contrast, fluorescence contrast imaging requires administration of a contrast agent. Further, in the method of irradiating light on the outer periphery of the breast base and analyzing the abnormal part from the whole breast image, the optical path difference is large between the image near the nipple and the peripheral image of the breast. Further, the degree of attenuation of scattered light changes due to changes in the shape of the breast. For this reason, there is a problem in identification of an abnormal site and diagnosis accuracy. Japanese Patent Laid-Open No. 2002-272745 (Patent Document 6) presses and flattens the breast by pressing an applicator to eliminate or reduce this phenomenon. However, this increases the size of the apparatus and is similar to conventional mammography. Accompanied by discomfort. Therefore, none of them are suitable for the purpose of self-examination of breast cancer for women at risk of illness at home.

The present invention relates to a diagnostic apparatus capable of observing and photographing a subcutaneous blood vessel distribution non-invasively and simply and analyzing the photographing result, and an analysis system thereof. Tumors that can be made close to the skin, such as difficult breast cancer and skin cancer, can be easily tested at home.
The angiography apparatus of the present invention and its blood vessel distribution analysis system have the following configuration.
[1] Probe light emitted from the irradiation unit, including an irradiation unit that can irradiate probe light toward the inspection target region and an imaging unit that receives scattered light and / or transmitted light from the inspection target region irradiated with the probe light An angiography apparatus is configured so as not to directly enter the imaging unit.
[2] 1) A hollow body that has an open end that can be brought into close contact with the inspection target site, and that receives a part of the inspection target site when the open end is in close contact with the inspection target site;
2) An irradiating unit that is provided at or near the edge of the open end and can irradiate probe light toward a site to be inspected received in the hollow body;
3) The angiography apparatus according to 1 above, further including an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the inspection target site irradiated with the probe light toward the hollow body.
[3] The angiography apparatus according to 2 above, further comprising a decompression unit for sucking a part of the examination target portion into the hollow body.
[4] The probe light emitting portion of the irradiating portion is provided in the hollow body, and the probe light or its reflected light is directly incident on the imaging portion by being covered with the inspection target portion received inside the hollow body. 4. The angiographic apparatus according to 2 or 3, which is obstructed.
[5] 1) A hollow body having an open end in a shape capable of being in close contact with a region to be examined,
2) An irradiation unit that is provided at or near the edge of the opening end and can irradiate the probe light toward the inspection target portion facing the opening in the hollow body or the vicinity thereof,
3) The angiography apparatus according to 1 above, further including an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the inspection target site irradiated with the probe light toward the hollow body.
[6] The probe light emitting portion of the irradiating portion is provided at an edge of the opening end, and is covered with the inspection target portion that is in close contact with the hollow body opening portion, so that the probe light or its reflected light is applied to the imaging portion. 6. The angiography apparatus according to 5 above, wherein direct incidence is prevented.
[7] The angiography apparatus according to any one of 2 to 6, wherein the hollow body wall is impermeable to probe light.
[8] The angiography apparatus according to any one of 1 to 7, wherein the probe light is near infrared light.
[9] The angiography apparatus according to 8, wherein the near-infrared light is near-infrared light having a hemoglobin absorption wavelength.
[10] The angiography apparatus according to any one of 1 to 9, wherein the examination target site is skin and / or subcutaneous tissue.
[11] The angiography apparatus according to 10, wherein the examination target part is a part of a breast.
[12] The angiography apparatus according to any one of 1 to 11, wherein the blood vessel is a cutaneous vein.
[13] The angiography apparatus according to any one of 1 to 12, wherein the imaging unit includes a CCD camera.
[14] The angiography apparatus according to any one of 1 to 13, further including means for specifying an imaging position.
[15] The angiography apparatus according to 14, wherein the imaging position is specified by measuring distances and angles from a plurality of reference positions.
[16] The angiography apparatus according to 14, wherein the imaging position is specified by measuring a moving direction and a moving amount from the reference position.
[17] The angiography apparatus according to 14, wherein the imaging position is specified by analyzing a captured image.
[18] The angiography apparatus according to any one of 1 to 17, wherein the irradiation unit includes a plurality of light source rows or arrays or a plurality of optical fiber open end rows or arrays connected to the light sources.
[19] A blood vessel abnormality diagnosis device including the angiography device according to any one of 1 to 18 above, a display device that displays a captured image, and / or a storage device that stores image data.
[20] The image data stored in the storage device includes reference data for a normal part and reference data for an abnormal part, and the abnormality of the blood vessel image in the photographed image is determined by comparing the photographed image with these reference data. 20. The blood vessel abnormality diagnosis device according to 19 above.
[21] The angiography apparatus according to any one of 1 to 18 or the vascular abnormality diagnosis apparatus and the blood vessel distribution analysis apparatus according to any one of 19 to 20, which are acquired by the angiography apparatus or the vascular abnormality diagnosis apparatus A blood vessel abnormality diagnosis system that analyzes the obtained data and determines a blood vessel abnormality.
[22] A blood vessel distribution analyzing apparatus including means for calculating light and darkness of an entire image photographed by any one of the devices 1 to 18 and determining the blood vessel distribution by comparing the lightness and darkness of each part of the image.
[23] A grayscale value at a position having the largest grayscale value in the photographed image is obtained, an average grayscale value in the area is obtained while the area is expanded to include the position, and an inflection point of the grayscale value is obtained. 23. The blood vessel distribution analyzing apparatus according to 22 above, in which a boundary between regions corresponding to is determined as a blood vessel distribution region boundary.
[24] Of the captured image, the portion to be analyzed is divided into k regions, the gray scale value of each region is obtained, and then the number of divisions is reduced while increasing the area of each region. The gray scale value is obtained, this step is repeated until k = 1, and the blood vessel distribution of the above 23 is included, including means for determining the blood vessel distribution based on the change of the gray scale value in the corresponding region between the steps. Analysis device.
[25] Of the photographed image, the part to be analyzed is divided into non-overlapping polygonal areas of equal area, the grayscale value of each area is obtained, and then the area with the lowest grayscale value is selected. A means for determining a distribution of blood vessels based on a change in gray scale value between steps by obtaining each gray scale value by combining each of the high areas with their adjacent areas, obtaining each gray scale value, and repeating this step; 24. The blood vessel distribution analyzing apparatus according to 24.
[26] The device according to any one of the above 19 to 25, which diagnoses the presence / absence of an abnormal site of angiogenesis and / or the progress of abnormality based on the analysis result of blood vessel distribution.
[27] A breast cancer diagnostic apparatus for diagnosing breast cancer by determining vascular abnormalities with the apparatus according to 26.
[28] A breast cancer diagnostic method using the breast cancer diagnostic apparatus according to [27].
By using the angiography apparatus of the present invention and the blood vessel distribution analysis system of the present invention, blood vessel distribution can be observed and photographed non-invasively and easily, and the photographing result can be analyzed. Tumors that can be made close to the skin, such as difficult breast cancer and skin cancer, can be easily tested at home.

FIG. 1 is a schematic diagram showing an embodiment of the angiography apparatus of the present invention.
FIG. 2 is a schematic diagram showing the operation principle of the angiography apparatus of FIG.
FIG. 3 is a schematic diagram showing a conventional apparatus using reflected light in contrast to the apparatus shown in FIG.
FIG. 4 is an explanatory diagram showing a configuration example of the blood vessel distribution analysis system of the present invention.
FIG. 5 is a schematic diagram showing an example of blood vessel distribution between a normal site and an angiogenesis site examined by the blood vessel distribution analysis system of the present invention.
FIG. 6 is a diagram (depopulated distribution) showing an outline of a region segmentation by a captured image and distribution analysis system by the angiography apparatus of the present invention.
FIG. 7 is a diagram (dense distribution) showing an outline of region segmentation by a captured image and distribution analysis system by the angiographic apparatus of the present invention.
FIG. 8 is a graph showing changes in the average gray scale value accompanying the enlargement of the selected area of the photographed images of FIGS.
FIG. 9 is a schematic diagram showing an aspect of the light irradiation unit of the angiography apparatus of the present invention.
FIG. 10A is a schematic diagram showing another embodiment of the angiography apparatus of the present invention, and FIG. 10B is a schematic cross-sectional view corresponding to this.
FIG. 11 is a schematic diagram showing still another aspect of the angiography apparatus of the present invention.

The angiography apparatus and the blood vessel distribution analysis system of the present invention will be described below.
An angiography apparatus of the present invention includes an irradiation unit that can irradiate probe light toward a region to be inspected and an imaging unit that receives scattered light and / or transmitted light from the region to be inspected that has been irradiated with the probe light. The emitted probe light is configured not to directly enter the imaging unit.
Specifically, various aspects can be included, but typically, as the first aspect,
1) a hollow body having an open end that can be in close contact with a region to be inspected, and receiving a part of the region to be inspected when the open end is in close contact with the region to be inspected;
2) An irradiating unit that is provided at or near the edge of the open end and can irradiate probe light toward a site to be inspected received in the hollow body;
3) including the angiography apparatus having an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the examination target site irradiated with the probe light into the hollow body, and as a second aspect,
1) a hollow body having an open end in a shape capable of being in close contact with a region to be examined;
2) An irradiation unit that is provided at or near the edge of the opening end and can irradiate the probe light toward the inspection target portion facing the opening in the hollow body or the vicinity thereof,
3) The angiography apparatus including an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the examination target irradiated with the probe light toward the hollow body.
FIG. 1 shows an example of the embodiment of the first aspect of the angiography apparatus of the present invention. This is an example in which the hollow body is a cylindrical body, and is largely composed of the following three parts.
1) A hollow body having a shape of an open end that can be brought into close contact with the inspection target portion, and receiving a part of the inspection target portion therein when the open end is brought into close contact with the inspection target portion [cylinder (1)] ,
2) An irradiator (2) provided at or near the edge of the open end and capable of irradiating the probe light toward the inspection target site received in the cylinder,
3) An imaging unit (3) that receives scattered light and / or transmitted light from the inside of the inspection target portion irradiated with the probe light.
As shown in FIG. 2, the first major feature of the angiography apparatus according to the first aspect of the present invention is that the site to be examined is taken into the apparatus (FIG. 2 (B)), and the probe light p is emitted from the side surface. By irradiating, the scattered light and / or transmitted light s from the inside of the site to be examined is photographed (FIG. 2C).
For this purpose, the imaging apparatus of the present invention has an opening end shaped so as to be in close contact with the inspection target region, and a part of the inspection target region ( 21) It has a hollow body [tubular body (1)] for receiving it inside. If the body part to be inspected is a body part rich in elasticity, the opening end is shaped so as to be in close contact with it, and the opening end is pressed against the body part to be inspected so that a part of the body part to be inspected is pushed inside. However, preferably, the inside of the hollow body [tubular body (1)] can be decompressed so that the site to be inspected is drawn into the inside (see FIGS. 2B and 2C).
The shape of the hollow body [tubular body (1)] is not particularly limited as long as a photographing unit described later can be provided, and may be a cylindrical body such as a cylinder or a rectangular tube, but is spherical (however, has an open end), hemisphere The shape may be any shape such as a truncated cone, a truncated cone or a truncated pyramid. Here, the hollow body only needs to be of a size that allows the region to be inspected to be taken inside, and as long as it has a hollow portion as long as it is provided. As long as the effect is obtained, a pair of opposing rib-like members may be used. However, when the cross-sectional shape of the opening end is square, the distance traveled through the inspection target site when the probe light is irradiated from the inner periphery of the opening end differs between the apex and the side, so at least the cross-sectional shape of the opening end is A circle or an ellipse, particularly a circle, is desirable.
The opening end diameter of the hollow body (1) is usually about 0.5 to 10 cm, preferably about 1 to 5 cm, although it depends on the size of the region to be examined. If the open end is too small, the inspection efficiency is poor, and the taking-in of the inspection target part into the cylinder does not proceed smoothly. On the other hand, if the opening end is too large, the absorption of the probe light in the region to be inspected becomes large and sufficient inspection cannot be performed.
When the pressure inside the hollow body (1) is reduced, the means is not particularly limited. For example, as shown in FIGS. 1 and 2, a tube or the like is pulled out from a part of the cylinder, and the other end is connected to a pressure reducing device. For the decompression device, any means such as a decompression device by reciprocating movement of a piston, a rotary motor or an eccentric motor, a decompression pump by a cyclone method, etc. can be used, but in the case of self-examination of breast cancer, a motor type decompression pump is used. preferable. In the case of self-examination, a switch of a decompression device may be attached to a cylinder or the back of an imaging unit (3) described later so that suction can be performed at a desired position while being operated. In addition, the cylinder, the decompression device, or the pipe connecting the cylinders, so that the decompression does not become excessive, or the decompression is maintained at a constant level, or the inside of the cylinder can be quickly returned to the atmospheric pressure at the end of shooting. A hole that can be opened and closed and valve means may be provided as appropriate. Any means known to those skilled in the art can be used as the means for adjusting the degree of decompression.
The material of the hollow body (1) is not particularly limited, but it is preferable that the hollow body (1) is easily processed and has a certain pressure resistance, and at least the inner surface thereof is made of a material that easily absorbs probe light (for example, near infrared rays) described later. In addition, the opening is preferably made of a material that allows easy installation of a light emitting means to be described later and has excellent adhesion to a region to be examined (for example, skin). Each part may be made of a separate material so as to meet these conditions.
The degree of decompression depends on the flexibility of the target part, the opening end diameter, and the like, but the target part may be drawn into the opening end by about 2 to 5 mm at least. For example, when the target site is skin, the pressure may be reduced from atmospheric pressure to about 1 to 100 hPa. If the pressure becomes higher than this, the subject may feel pain in the reduced pressure part.
The irradiation part (2) is provided in the opening edge part of the hollow body (1) or its vicinity as shown in FIG.1 and FIG.2 (A). For example, the light emitting means may be arranged along the opening end of the hollow body (1) with the inner side facing the edge. The light emitting means is typically a light emitting diode (LED). The probe light has a wavelength that is relatively well transmitted through living tissue and is preferably absorbed by blood vessels, particularly hemoglobin, but near-infrared light having a wavelength of 700 to 900 nm is relatively well transmitted through living tissue, while The hemoglobin in the erythrocytes that flow through it specifically absorbs near-infrared light of 850 nm, so that near-infrared light in the above-mentioned wavelength range is preferable. A light emitting diode may be used in combination of a plurality of wavelength regions. For example, when hemoglobin binds to oxygen, its absorption characteristics change depending on the state of the hemoglobin, so that it is possible to measure both the absorption wavelength of oxygenated hemoglobin (oxyhemoglobin) at 850 nm and the absorption wavelength of deoxygenated hemoglobin (deoxyhemoglobin). You may enable it to switch the wavelength of LED light irradiated to. The probe light may be a normal light beam or a laser beam.
In addition, as shown to FIG.1 and FIG.2 (A), it is preferable to provide LED equally along the inner periphery perimeter. As shown in FIG. 1 and the like, it is preferable to provide them as densely as possible, but they may be provided at intervals. Moreover, when using LED of a some wavelength range as mentioned above, you may install combining each. Further, when the inside of the hollow body (1) is depressurized, the surface Ψ in contact with the target part is inclined as shown in FIG. You may have the shape.
The imaging unit (3) is provided at a position opposite to the opening as shown in FIG. For example, when the hollow body (1) has a rotationally symmetric shape (for example, a cylindrical shape), the hollow body (1) is provided on the surface facing the opening on its axis. However, if necessary, the probe light scattered and transmitted from the target site may be drawn out of the hollow body (1) through, for example, an optical fiber and guided to an imaging unit provided separately. The irradiation section is typically a circular column as shown in the above example, but it may be an array extending in two dimensions.
The imaging unit (3) typically includes a transparent partition (for example, glass or polycarbonate plate) and / or an optical system (for example, a lens) (4), a camera holder (5), An imaging means (for example, a CCD substrate) (6) is included. The transparent plate is provided for the purpose of avoiding the influence of the pressure change in the cylinder, preventing the degree of decompression in the cylinder from being lowered, and limiting contamination by sebum. The optical system (4), camera holder (5), and imaging means (6) can be configured using configurations, materials, and structures known to those skilled in the art. These may be any one that can detect the probe light, and those commercially available as a CCD camera unit or the like may be used. In the present invention, shooting includes not only still image shooting but also moving image shooting. Therefore, for example, it is possible to obtain a three-dimensional image in the vertical direction of the target part by performing imaging while sucking the target part and performing differential processing on the images of the frames.
For example, in the case of a biometric authentication system used in a bank or the like, as shown in FIG. 3, the probe light p is emitted from a position facing the inspection target part toward the inspection target part. For this reason, even if the imaging unit is provided at a position opposite to the opening, most of the incident light to the imaging unit is reflected light r from the target surface (for example, the skin surface) and the inside of the target part (for example, Only a small amount of information is available from the skin. On the other hand, in the present invention, since scattered light and transmitted light from the inside of the target site (for example, intradermal) are photographed, information from the inside of the target site (for example, intradermal) can be acquired with high efficiency. In particular, when the surface of the probe light emitting part is covered with the target part (becomes in a close contact state), reflected light from the target part surface is not mixed as noise into the imaging part, which is preferable.
In the above case, if the area or volume of the target part is large, the probe light does not sufficiently penetrate into the target part, or the light scattered from inside the target part does not have a sufficient amount of light, and the center of the target part In some cases, a good image may not be obtained. However, even in this case, it is possible to obtain effective information about the ring-shaped portion excluding the central portion. Therefore, the present invention includes an apparatus that acquires not only the entire surface to be examined but also a part of the captured image.
The captured image data may be input, displayed, or stored in a blood vessel distribution analysis system described below or other display device or storage device (collectively represented as “computer” in FIG. 1).
The site to be inspected by the angiography apparatus of the present invention is not particularly limited as long as it is an accessible site, but usually skin of humans or animals, particularly a hairless or substantially hairless skin surface is preferable. Flexible skin and / or subcutaneous tissue is preferred. Application to a site rich in subcutaneous fat, for example, the breast and the vicinity thereof is suitable, and in this respect, it is particularly suitable for angiography for diagnosis of breast cancer.
The second embodiment of the device of the present invention is as shown in FIG.
1) A hollow body (1) having an open end shaped so as to be in close contact with a region to be examined
2) an irradiation unit (2) provided at or near the edge of the opening end and capable of irradiating probe light toward a region to be examined facing the opening in the hollow body or the vicinity thereof;
3) It has an imaging unit (3) for receiving scattered light and / or transmitted light (indicated by s) emitted from the inside of the examination target irradiated with the probe light into the hollow body.
The major difference from the first aspect is that the probe light is irradiated from the edge of the opening end or the vicinity thereof to the inspection target part or the vicinity thereof without including the imaging part into the hollow body. is there.
This aspect is suitable for photographing a blood vessel image at a relatively shallow position as compared with the first aspect. Further, since the target site is not taken into the hollow body, for example, it is suitable for continuous scanning by smoothly scanning the surface of the skin.
In the second embodiment, the position of the irradiation unit is not limited, but it is convenient to provide the irradiation unit outside the hollow body as shown in FIG. In this case, since the probe light from the irradiation unit is completely blocked from the imaging unit by the wall surface of the hollow body, it is possible to increase the probe light output and obtain information up to a deeper part. Thus, in the second aspect. The hollow body should just have a function which the wall surface optically shields between a probe light irradiation part and an imaging | photography part (light-receiving part) substantially. Such materials are determined by the wavelength of the probe light, but an example of near infrared light is vinyl chloride.
However, it is also possible to provide both the irradiation part (2) and the photographing part (3) in the hollow body by providing the shielding member (22) inside the hollow body as shown in FIG.
In the case of FIG. 11, since it can also be used in the first mode, it is possible to scan the surface of the target part widely, and when a detailed examination is required, it is possible to perform imaging by taking a deeper part.
In this second aspect, particularly when the irradiation unit (2) is provided outside the hollow body as shown in FIG. 10, the optical axis is inclined so that the probe light p sufficiently enters the target site under the imaging unit. It is preferable to make it. Although it depends on the position where the irradiation unit (2) is provided, the irradiation angle θ (the probe light incident angle on the surface of the target site) is preferably approximately 10 degrees or more, and more preferably 30 degrees or more. If the irradiation angle θ is too large, the depth of penetration into the skin will be small, so 80 degrees or less is preferable, and 60 degrees or less is more preferable. In addition, an irradiation element such as an LED arranged in an annular shape or a plurality of housings that house the irradiation element may be interlocked and inclined so that the irradiation angle θ is variable. Such a configuration, for example, provides a concentric double ring structure with different diameters, and supports an irradiation element such as an LED on the inner and outer rings or a plurality of housings housing this, respectively, near the center and near the outer periphery, This can be realized by changing the relative vertical relationship between the inner and outer rings. You may enable it to operate the position of any ring directly from the exterior of a hollow body. For example, an annular member that is rotatably screwed on the outer periphery of the hollow body is provided, and this is coupled to one of the rings. The other ring is fixed in the hollow body. By rotating the annular member, the annular member moves up and down on the outer periphery of the hollow body, so that the relative position of the inner and outer rings changes, and the inclination of the irradiation element changes. The inclination angle may be adjusted electrically with a stepping motor or the like.
In the second embodiment, a lid member that is in close contact with the skin may be provided at the hollow body opening. The lid member is made of a material that transmits light having the same wavelength as the probe light.
The apparatus according to the present invention may include means for specifying the photographing position (hereinafter referred to as localization means) in both the first aspect and the second aspect.
Such localization means may include various types, but roughly classified into the following four types.
(A) Measuring relative position from a reference position.
(B) Measuring the amount of movement from the reference position.
(C) The position is specified based on the photographed image.
(D) A mark or other coordinates are provided on the target part.
Hereinafter, a case where the operator performs angiography in the vicinity of his / her breast will be briefly described as an example.
In the configuration (a), a reference position is set at the time of photographing, and a relative position from the reference position is measured. This is typically based on the same principle as triangulation.
Although the reference position can be arbitrarily selected, for example, the left and right ends of the pelvis (respectively L point and R point) can be used as the reference position. The photographing apparatus is combined with these reference positions in some way, and when photographing is performed at a certain point P, the photographer operates the distance LP from the point L and the distance RP or ∠PLR from the point R and ∠PRL is recorded in association with the captured image. Since the L point and the R point are fixed points, and the P point exists on the skin surface of the operator, the position of the P point is almost uniquely determined by the above information (distance or angle). If necessary, a third reference point may be provided to measure the same distance and angle as described above.
The coupling between the photographing apparatus and these reference positions may be mechanical or may use sound, light, radio waves, or the like.
Examples of the mechanical configuration include a belt-like member having a size suitable for being fitted on the waist and two cord feeding devices provided on the belt-like member. When the operator wears the belt, two cord feeders (C ₁ And C ₂ ) Is fixed at positions corresponding to both ends of the pelvis, for example. The cord feeding device includes a winding shaft for winding the cord therein, and further includes a housing having an opening for feeding the cord and rotatably supported around the winding shaft. The take-up shaft is urged in a direction in which the cord is pulled in by a winding spring, for example.
At the time of photographing, a cord is pulled out from each reel-shaped device and connected to the photographing device. Since the opening for feeding the cord can rotate about the winding shaft, the opening rotates following the photographing apparatus when the photographing apparatus is moved. Accordingly, if the urging force is set so that a sufficient tension is generated in the cord, the winding shaft-opening-imaging device is arranged substantially in a straight line. ₁ And C ₂ Each angle ∠PC ₁ C ₂ And ∠ PC ₂ C ₁ Corresponds to the aforementioned ∠PLR and ∠PRL. Also, the length of each cord drawer PC ₁ And PC ₂ Corresponds to the aforementioned LP and RP. Angle PC ₁ C ₂ And ∠ PC ₂ C ₁ Since it can be easily calculated from the rotation angle of the opening and the rotation angle of the winding length of the cord, the photographing position can be specified by providing means for measuring these rotation angles. Here, what is collectively referred to as a cord is a line, string, chain, or the like that does not adversely affect measurement when a sufficient tension is applied, and can be formed of resin, paper, other fibers, metal, or the like. .
Examples of configurations using sound, light, radio waves, etc. include, for example, communication means (C ₁ And C ₂ ) Is provided in the form of a belt instead of the above-described cord feeding device. In this case, the photographing devices P and C are provided by providing a device that detects sound, light, or radio waves in a part of the photographing device or by providing a device that emits sound, light, or radio waves. ₁ And C ₂ Are each acoustically, optically or electromagnetically coupled and have a distance PC ₁ And PC ₂ Is easily determined (eg, C ₁ Multiply the propagation time of the ultrasonic waves emitted from the sound speed by the distance PC ₁ Is obtained. ). Angle PC ₁ C ₂ , PC ₂ C ₁ In addition, since an ultrasonic wave, light or radio wave irradiation angle and / or reception angle is easily measured by using a mechanical drive or an array or the like, the photographing position can be specified.
In addition, in the case of a mechanical configuration and a configuration using sound, light, radio waves, etc., the distance PC ₁ And PC ₂ The rough shooting position is specified only by the angle, but the angle ∠PC ₁ C ₂ , PC ₂ C ₁ It is also preferable to measure together. Further, the elevation angle from the skin surface to the imaging device may be measured. Moreover, you may make it mount | wear near a scapula instead of the belt wound around a waist.
In the configuration (b), a reference position is set at the time of shooting, and a moving distance from the reference position is measured. This is typically based on the same principle as a mechanical or optical mouse.
The reference position may be an arbitrary position, and may be based on a physical feature point (a position such as a mole) or a fixed point (for example, the lower edge between both breasts). It is preferable to record. This can also be realized by providing the imaging device with a visible region imaging device so that a visible image can be captured by the imaging device, or by providing a character input device.
In the case of the mechanical type, the ball is typically coupled to the photographing apparatus in a rotatable manner. This can be realized by sealing the ball in the housing so that a part of the position is exposed outside the housing, and connecting the housing to the imaging device, as seen in the position identification part of the computer mouse. The rotation direction and rotation angle of the ball are measured by, for example, irradiating light beams from two or more directions (this method may be a conventional method), and the movement distance and direction are measured by calculation.
In the case of the optical type, visible light or infrared light or a laser beam thereof is irradiated on the skin surface. In the case of infrared light, probe light may be used in combination. Reflected, transmitted or scattered light is taken into the imaging apparatus (which may be the hollow body described above or a light receiving unit may be provided separately), and some feature points are identified by a CCD or the like. When the photographing apparatus is moved, these feature points move in the photographed image, and the moving direction and the moving distance are measured by analyzing them. Note that probe light irradiation, light reception, and position measurement are unitized in an existing optical mouse, which may be used in the present invention.
The moving distance can be measured by an acoustic method and a radio wave method. For example, the moving distance can be obtained by irradiating the skin surface with a sound wave or an electromagnetic wave obliquely, measuring the moving speed by Doppler shift at the time of movement, and integrating this with time. This method can also be used by an optical method if the detection accuracy is high.
The configuration of (c) specifies a position based on a captured image. (C-1) A configuration in which a visible image is also captured and specified at the time of shooting, and (c-2) is analyzed at the time of shooting. An example is a configuration that specifies the position based on the blood vessel image.
The configuration of (c-1) can be realized, for example, by providing a visible image capturing device in addition to the hollow body described above and capturing a visible image in conjunction with the capturing of a blood vessel image. In this case, the visible image may be obtained by superimposing the imaging region as a visible image, or the peripheral image may be captured at a wide angle so that the position can be specified.
In the configuration (c-2), the imaging position is localized by correspondence with a blood vessel substantially in a fixed position.
In the configuration (d), a mark or other coordinates are provided at the target position. As an example of such a mode, there is a method of attaching a sheet or the like that is in close contact with the skin on which coordinates or the like are drawn. For example, in the case of photographing a breast, a cup-type bra or the like in which coordinates and markers that can be visually recognized with visible light are drawn in advance. Shooting is performed by superimposing infrared and visible light on the cup-shaped brassiere, and the two are linked to specify the position of each captured image. As the cup-type brassiere or the like, it is preferable to use a skin-contact type because there is almost no displacement during photographing. A similar planar sheet may be used for portions other than the breast.
Alternatively, the coordinates may be drawn with ink that is difficult to see on the skin in the visible range, for example, close to skin color, and the two may be linked by performing imaging in a wavelength range corresponding to the complementary color of skin color simultaneously with infrared imaging. When drawing the coordinates with ink, the cup-shaped brassiere described above can be used as a template, or the coordinates drawn on the transfer sheet can be affixed on the breast, and the sheet can be peeled off to transfer the coordinates onto the breast. it can.
When photographing from above a cup-type brassiere or the like, the second aspect is preferred, but in the latter case, both the first and second aspects are possible.
The localization means may be combined with either the first aspect or the second aspect. In particular, when combined with the second aspect, the operator can easily scan and image the target region widely. It is possible to obtain the distribution of blood vessels under the skin of the target site (for example, breast) together with its position information with high accuracy over a wide range, even though it is a simple device with little burden on the user. For example, a plurality of frames are photographed per second, and the photographed image and the position information are recorded together. If the obtained blood vessel image is mapped according to the position information, diagnosis of blood vessel abnormality becomes easier.
As described above, the main part of the apparatus of the present invention has been described with respect to two typical embodiments. However, the probe light emitted from the irradiation unit does not directly enter the imaging unit, and scattered light or transmitted light emitted from the target site is not used. An apparatus that receives light at the imaging unit, particularly an apparatus in which the irradiation unit and the imaging unit are fixed in a fixed positional relationship, particularly a small-sized angiographic apparatus is included in the scope of the present invention.
The apparatus of the present invention may further include an apparatus for displaying a photographed image. The captured image is displayed on a display device (CRT, liquid crystal display, etc.), and the operator can view it in real time or as a recorded image.
The present invention also includes a blood vessel distribution diagnostic apparatus including a blood vessel distribution analysis system. Hereinafter, the configuration will be described.
The blood vessel distribution analysis system includes an entire system for analyzing a captured image. For example, a known method can be used as a method of extracting a dark part or the like from a captured image by image analysis. In the present invention, for example, it is possible to take a method of calculating the brightness of the entire image and determining the distribution of blood vessels based on this and the brightness of each part of the image.
That is, the brightness of the image may vary depending on the shooting conditions, but the blood vessel distribution can be extracted by subtracting the brightness of the entire image from the brightness of each part of the image. The blood vessel distribution area can also be determined from local changes in brightness.
Although the method is not particularly limited, as an example of a method for determining a blood vessel distribution area from local changes in light and darkness, the darkest position (a position having a large gray scale value in an imaged image. (Hereinafter, also simply referred to as the darkest point), and a method of obtaining an average grayscale value of an enlarged region while enlarging the region so as to include the portion can be cited. For example, circles with a radius r centering on the darkest point are drawn one after another, and an average gray scale value inside is calculated. Thereby, in the said image, an average gray scale value can be prescribed | regulated as a function with respect to r. Since r = 0 is the darkest point, the average grayscale value gradually decreases as r increases, but the decrease rate is low as long as the blood vessel is present. On the other hand, when the circle reaches an area where blood vessels are not distributed, the average gray scale value is greatly reduced. That is, the concentration region of the blood vessel distribution can be defined by looking at the change in the average gray scale value reduction rate. In this example, the circle drawn around the reference point was expanded, but the change in the grayscale value was examined two-dimensionally from the reference point in multiple directions, and the grayscale value on each line and its The concentration region of the blood vessel distribution may be defined by looking at changes (for example, inflection points).
In addition to expanding the region from the darkest point, the region may be expanded from the brightest point, or the region may be expanded from both. Alternatively, a plurality of reference points (which may be grid points corresponding to predetermined coordinates in the photographed image or points that are presumed to be a blood vessel distribution site from the gray scale value) in the image area are taken, and the same as above It is also possible to estimate the concentration region of the blood vessel distribution by calculating the average gray scale value and its change (for example, inflection point) while enlarging the region.
In the above method, since the rate of change is viewed instead of the absolute value of the gray scale value, it is possible to eliminate errors caused by non-uniformity of the probe light distribution caused by the inclination of the measuring device, the bias of the target part pull-in, or the like. it can.
Further, in the present invention, the portion to be diagnosed in the captured image is more simply divided into k regions, and the gray scale value of each region (the average value in the region, unless otherwise specified, Next, the number of divisions is reduced while increasing the area of each region to obtain the gray scale value of each region. This step is repeated until k = 1, and the corresponding region between steps is determined. The distribution of blood vessels can be determined based on the change in the gray scale value.
In the above method, a unit area (divided individual area) a in a certain step _i Is the corresponding unit area a in the next step _{i + 1} The gray scale value g _i , G _{i + 1} Is g _i > G _{i + 1} Then, a brighter region (that is, a region having a small blood vessel distribution in the positive image) is captured by enlarging the unit region. That is, the blood vessel distribution is a _i Than a _{i + 1} Is sparser. On the other hand, g _i <G _{i + 1} Then the blood vessel distribution is a _i Than a _{i + 1} Is denser. By repeating this step until k = 1 (that is, the unit region = the entire portion to be diagnosed), the density of the blood vessel distribution in each portion can be determined. In this method, since the density between adjacent regions is determined, an overall error (for example, when the apparatus is pressed against the region to be inspected) that can occur when the gray scale values of k regions are simply compared. (Such as an angle at the time of shooting), which can cause a bias of light and darkness of the entire photographed image, which can be caused by operation. In practice, it is not necessary to identify individual blood vessels in diagnosis of cancer or the like, and its density is important, and the present invention provides an efficient diagnosis method for cancer and the like.
Here, the minimum unit area (that is, the k areas initially set in the above example) only needs to be comparable to the minimum size of the tumor from which angiogenesis starts. In the present invention, as described above, for example, a circular area can be imaged, and an annular area excluding the central part can be determined. The “part to be” refers to a partial region of such a captured image.
Although the shape of each unit region is not limited, it is preferably divided into polygons having the same area without overlapping, for example, a triangle, a rectangle, and a hexagon (particularly, a regular triangle, a square, and a regular hexagon). In the case of squares, the simplest way is to cut out the captured image as the largest square inscribed in the part to be diagnosed, divide it into m squares, and obtain the gray scale value of each area. Record the highest and lowest values (step 0). Next, n squares adjacent to the periphery of the unit area showing the highest value and the lowest value are added, and the average clay scale value is calculated (first step). Considering the case where the unit area of the maximum value and the minimum value is located on the edge of a square cut out from the image, the number of squares added in the first step n ₁ Is 3 ≦ n ₁ ≦ 8, the number of squares added sequentially adjacent to its perimeter n _{1 ・ 2 ・ 3 ...} Is 3 · 5 · 7 ··· n _{1 ・ 2 ・ 3 ...} It increases in the range of ≦ 8 · 16 · 25. The gray scale values of all the unit areas sequentially added are added to obtain the average value sequentially, and the change in the gray scale values of the highest value and the lowest value is examined.
When looking at a blood vessel concentration site, the change in grayscale value between steps is relatively slow. On the other hand, when blood vessels are sparsely distributed, a region that does not include blood vessels is captured between steps, resulting in a large change in gray scale value. Note that, by examining the change from the minimum gray scale area together with the change from the maximum gray scale value area, it is possible to make a determination that does not depend on the brightness of the entire captured image.
Data analysis for these image analysis, region segmentation, grayscale value calculation, determination, site-by-site and / or analysis of changes over time, and switching when using multiple probe light wavelengths, Communication and the like can be controlled by control means such as a computer. In addition, a switch may be attached to any part of the above device so that the operator can easily operate it, and the device further has an external input device (wired, wireless, light, ultrasonic, etc.). Further, suction and release thereof, probe light irradiation, imaging, and the like may be controlled by a remote controller or the like. An example of the configuration diagram of such a system is shown in FIG. That is, this system includes an irradiation unit (2) for irradiating probe light to a hollow body (1) that receives a region to be inspected, and an imaging unit (3), and the imaging unit includes an imaging means (6). (1) is connected to the decompression means (8), and the irradiation section (2), decompression means (8), and imaging means (6) are connected to the computer (10) via the control section (12). ing. Here, the control unit (12) is, for example, a switch, and may control all or a part of irradiation, decompression, and imaging, and these may control a computer (10 without going through the control unit (12). ) May be connected. In particular, the data obtained by the imaging means (6) may be transmitted directly to the computer (12). The display device (9) is optional, but is usually necessary when a doctor or the like directly performs an image diagnosis. The display device (9) may display information that guides the imaging procedure, or may display a visualization image of the imaging result or a determination result such as “no abnormality” or “needs specialist diagnosis”. The display device (9) may be a touch panel (for example, a liquid crystal panel) integrated with the control unit (12) or the computer (10).
In particular, when the above-described localization means is included, a chest image or the like can be presented by computer graphics, and a photographed image can be displayed while pointing the photographing region with a point or the like. In addition, it is possible for a specialist or the like to diagnose the captured image. In this case, the imaging system itself may not include a display device, or the display device or the like may be installed in a physically separated place. For example, an operator (which may be the subject himself / herself) operates the above-described imaging device to image the target portion, and records the image on an appropriate recording medium, or medical treatment through a communication line such as a telephone line or an optical fiber. It can be sent to institutions or data collection institutions where doctors can make a diagnosis.
The irradiation unit (2), the decompression unit (8), the imaging unit (6), and the display device (9) automatically irradiate the probe light after the suction under the control of the computer (10). It is good also as a structure which displays the propriety of the suction state and the angle with respect to the object part of an apparatus by measuring light quantity, and an imaging means (6) performs imaging | photography automatically under control of a computer (10), Among them, the optimum data may be selected. Further, the computer (10) may include a program for performing an arbitrary image processing step such as superimposing a plurality of times of data or taking a difference from a plurality of time series data.
According to the present invention, since an angiogenesis site as shown in FIG. 5 can be discriminated, the presence or absence of angiogenesis due to some cause can be discriminated. For example, in the case of breast cancer, angiogenesis associated with a tumor starts from about 2 mm in diameter of the tumor, and therefore can be identified as a concentration of blood vessels of 2 mm or more, so the apparatus of the present invention is effective as a diagnostic apparatus for breast cancer.

Hereinafter, the present invention will be described with reference to examples. The following examples are given to illustrate the present invention and are not intended to limit the present invention.
Example 1
48 near-infrared light-emitting LEDs (maximum wavelength: 850 nm, manufactured by Nisshin Denshi Kogyo Co., Ltd.) are attached to the opening of a cylinder made of vinyl chloride that does not transmit light with an inner diameter of 46 mm and a height of 100 mm, along the inner circumference. Near infrared light can be irradiated toward the center of the cylinder. In addition, on the opposite side of the cylinder, a CCD camera (XC-E150, 768 × 494 pixels manufactured by Sony Corporation, mount: C mount, flange back: 17.562 mm, outer dimension: width 29 mm, through a partition wall (glass plate) X height 29 mm x depth 32 mm) was fixed. Further, a tube having an inner diameter of 30 mm was passed through the side surface of the cylinder, and a suction device was attached to the other end so that the inside of the cylinder could be depressurized.
The above-mentioned device was pressed against the subject's chest, and photographing was performed. The results are shown in FIGS. FIG. 6 shows a case in which no set is seen in the blood vessel distribution (depopulated distribution), and FIG. 7 shows a case in which a set of blood vessels is seen (dense distribution). Select the unit area where the gray scale value is the highest value and the lowest value, respectively, and expand the selection area around the adjacent area (in the case of the highest value: (1) → (2) → (3) → (4) → (5) → (6) → (7), lowest value: [1] → [2] → [3] → [4] → [5] → [6] → [7]), average grayscale value Was calculated.
FIG. 8 shows the change of the average gray scale value accompanying the enlargement of the selected area. The upper graph in FIG. 8 is a graph in which no set is seen in the blood vessel distribution (depopulated distribution in FIG. 6), and the lower graph is a graph in which a set of blood vessels is seen (the dense distribution in FIG. 7). The average grayscale value in the bright part is indicated by ◯, and the average grayscale value in the dark part is indicated by ●. As shown in this figure, the gray scale value starting from the unit area showing the maximum value and the minimum value finally converges to the gray scale value of the entire image.
The slower the gray scale value decreases from the unit area where the gray scale value has the highest value to the surrounding area, the more the blood vessel aggregates, the greater the risk that a tumor exists. It is also possible to determine the presence or absence of angiogenesis by measuring over time.
Example 2
48 near-infrared light-emitting LEDs (maximum wavelength: 850 nm, manufactured by Nisshin Denshi Kogyo Co., Ltd.) are directed toward the opening surface on the outer periphery of a vinyl chloride cylinder that does not transmit light having an outer diameter of 43 mm and a height of 100 mm. It was attached at an angle of 45 degrees so that near infrared light could be irradiated. In addition, a CCD camera (XC-E150 manufactured by Sony Corporation, 768 × 494 pixels, mount: C mount, flange back: 17.562 mm, outer dimensions is provided on the opposite side of the cylindrical opening surface through a partition wall (glass plate). : Width 29 mm x height 29 mm x depth 32 mm).
In the same manner as in Example 1, the above-described device was pressed against the subject's chest and photographing was performed, and a blood vessel image near the skin could be obtained.
Example 3
A light irradiation / light reception unit of an optical mouse was attached to the same apparatus as in Example 2, and the obtained signal was configured to be input to a computer together with a photographed image.
In the same manner as in Example 1, a part of the subject's chest was used as a base point, and the device was moved little by little on the skin surface, and the image and position information were recorded simultaneously. By mapping this along the position information, a wide range of angiographic images could be obtained.
Comparative Example 1
Other than the configuration according to FIG. 3, an attempt was made to identify a blood vessel image by reflected light measurement using the same apparatus as in Example 1. However, almost all light input to the CCD camera is reflected light on the skin surface, which is significant. Measurement could not be performed.

  The angiography apparatus of the present invention can be manufactured at low cost, and can be easily miniaturized and the apparatus configuration is simple. Therefore, the angiography apparatus of the present invention is effective for imaging blood vessels at various sites, particularly blood vessel distribution near the skin surface. Therefore, it is particularly useful as a self-examination device for angiogenesis abnormalities near the skin surface, for example, breast cancer. In the apparatus of the present invention, the photographing unit and the irradiating unit are relatively close to each other, and can be configured substantially integrally. Therefore, it is useful as a simple inspection apparatus in which a subject holds and operates the apparatus in his hand and inspects himself / herself.

Claims (28)

An irradiating unit that can irradiate probe light toward the inspection target region and an imaging unit that receives scattered light and / or transmitted light from the inspection target region irradiated with the probe light, and the probe light emitted from the irradiating unit is an imaging unit An angiography apparatus characterized in that it is configured not to be directly incident on the light. 1) a hollow body having an open end that can be in close contact with a region to be inspected, and receiving a part of the region to be inspected when the open end is in close contact with the region to be inspected;
2) An irradiating unit that is provided at or near the edge of the open end and can irradiate probe light toward a site to be inspected received in the hollow body;
3) The angiography apparatus according to 1 above, further including an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the inspection target site irradiated with the probe light toward the hollow body. 3. The angiography apparatus according to 2 above, further comprising a decompression unit for sucking a part of the examination target portion into the hollow body. The probe light emitting portion of the irradiating portion is provided in a hollow body, and the probe light or its reflected light is prevented from being directly incident on the imaging portion by being covered by the inspection target portion received inside the hollow body. The angiography apparatus according to 2 or 3. 1) a hollow body having an open end in a shape capable of being in close contact with a region to be examined;
2) An irradiation unit that is provided at or near the edge of the opening end and can irradiate the probe light toward the inspection target portion facing the opening in the hollow body or the vicinity thereof,
3) The angiography apparatus according to 1 above, further including an imaging unit that receives scattered light and / or transmitted light emitted from the inside of the inspection target site irradiated with the probe light toward the hollow body. The probe light emitting part of the irradiation part is provided at the edge of the opening end, and the probe light or its reflected light is directly incident on the imaging part by being covered with the inspection target part closely attached to the hollow body opening part. 6. The angiography apparatus according to 5 above, which is obstructed. The angiography apparatus according to any one of 2 to 6, wherein the hollow body wall is impermeable to probe light. The angiography apparatus according to any one of 1 to 7, wherein the probe light is near infrared light. 9. The angiography apparatus according to 8, wherein the near infrared light is near infrared light having a hemoglobin absorption wavelength. 10. The angiography apparatus according to any one of 1 to 9, wherein the examination target site is skin and / or subcutaneous tissue. 11. The angiography apparatus according to 10, wherein the examination target part is a part of a breast. 12. The angiography apparatus according to any one of 1 to 11, wherein the blood vessel is a cutaneous vein. The angiography apparatus according to any one of 1 to 12, wherein the imaging unit includes a CCD camera.   The angiography apparatus according to any one of 1 to 13, further including means for specifying an imaging position.   15. The angiography apparatus according to 14, wherein the imaging position is specified by measuring distances and angles from a plurality of reference positions.   15. The angiography apparatus according to 14, wherein the imaging position is specified by measuring a movement direction and a movement amount from a reference position.   15. The angiography apparatus according to 14, wherein the imaging position is specified by analyzing a captured image.   18. The angiography apparatus according to any one of 1 to 17, wherein the irradiation unit includes a plurality of light source rows or arrays or a plurality of optical fiber open end rows or arrays connected to the light sources. 19. A blood vessel abnormality diagnosis device comprising the angiography device according to any one of 1 to 18, a display device that displays a captured image, and / or a storage device that stores image data. The image data stored in the storage device includes reference data of a normal part and reference data of an abnormal part, and the abnormality of the blood vessel image in the photographed image is determined by comparing the photographed image with these reference data. The vascular abnormality diagnosis apparatus described. The angiography apparatus according to any one of 1 to 18 or the blood vessel abnormality diagnosis apparatus according to any one of 19 to 20 and a blood vessel distribution analysis apparatus, the data acquired by the angiography apparatus or the blood vessel abnormality diagnosis apparatus A blood vessel abnormality diagnosis system that analyzes blood vessels and determines blood vessel abnormality. An apparatus for analyzing a blood vessel distribution, comprising means for calculating brightness and darkness of an entire image photographed by any one of the devices 1 to 18 and comparing the brightness and darkness of each part of the image to determine the blood vessel distribution. Obtain the grayscale value of the position with the largest grayscale value in the captured image, obtain the average grayscale value in the area while enlarging the area so as to include the position, and determine the grayscale value or a change in the blood vessel distribution area 23. The blood vessel distribution analyzing apparatus according to 22, wherein the boundary is determined. Of the photographed image, the part to be analyzed is divided into k areas, the gray scale value of each area is obtained, and then the number of divisions is reduced while the area of each area is expanded to reduce the gray scale value of each area. 24. The blood vessel distribution analysis device according to 23, further including means for determining the blood vessel distribution based on a change in gray scale value in a corresponding region between steps, by repeating this step until k = 1. . Of the captured image, the part to be analyzed is divided into polygonal areas of equal area that do not overlap, and the gray scale value of each area is obtained.Then, the areas with the lowest and highest gray scale values are selected. 25. The method according to 24, including means for determining each gray scale value by combining each adjacent area, obtaining each gray scale value, repeating this step, and determining a blood vessel distribution based on a change in the gray scale value between steps. Blood vessel distribution analysis device. The device according to any one of the above 19 to 25, which diagnoses the presence / absence of an abnormal site of angiogenesis and / or the degree of progression of an abnormality based on the analysis result of blood vessel distribution. 27. A breast cancer diagnostic apparatus for diagnosing a breast cancer by determining a vascular abnormality by the apparatus according to 26. A breast cancer diagnostic method using the breast cancer diagnostic apparatus according to 27.