WO2008010604A1

WO2008010604A1 - Blood vessel imaging device and system for analyzing blood vessel distribution

Info

Publication number: WO2008010604A1
Application number: PCT/JP2007/064619
Authority: WO
Inventors: Toshio Okazaki
Original assignee: School Juridical Person Kitasato Gakuen
Priority date: 2006-07-19
Filing date: 2007-07-19
Publication date: 2008-01-24
Also published as: JPWO2008010604A1

Abstract

A blood vessel imaging device for noninvasively and simply analyzing the distribution of veins. The device has an irradiation section for emitting probe light toward a target inspection portion and an imaging section for receiving dispersed light and/or transmitted light from the target inspection portion. The device is constructed so that the probe light emitted from the irradiation section does not directly enter the imaging section. Also provided are an analysis device for analyzing the result of imaging by the blood vessel imaging device and an analysis system for the result of imaging.

Description

Specification

Angiography equipment and blood vessel distribution analysis system

The present invention provides an apparatus for irradiating a target region including a blood vessel with probe light to image 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 the progress of Z or abnormality In particular, devices that irradiate the skin with near-infrared light and image the distribution 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) In addition, the present invention relates to an analysis system for discriminating the state of tissue inflammation or disease. Background art

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. If an abnormal lump is detected by palpation, mammograms (mammography) and ultrasonography (echography) should be used to check whether there is tissue deformation due to lesions in suspicious areas. If any abnormalities are found by these examinations, further examination of the living tissue (such as duct imaging, tumor marker examination, puncture aspiration cytology) will be performed to make a final diagnosis.

Recently, breast cancer testing has been encouraged for women over a certain age, but due to various reasons such as time constraints, the regular checkup rate is not necessarily high. this Therefore, for early detection of breast cancer, it is important that patients themselves conduct regular self-examination of the breast and find abnormalities at an early stage. However, it is difficult to determine the presence or absence of lumps by palpation by amateurs, and there are cases where abnormalities are overlooked and potential tumors that cannot be detected by palpation in the first place. It has been.

On the other hand, the method of detecting blood vessels in the living body by irradiating the skin with living tissue and irradiating near infrared light with a wavelength of 700 to 900 nm is used for diagnosis of cardiovascular function, blood volume and It is used for blood pressure measurement or biometric authentication.

For example, in Japanese Patent Application Laid-Open No. 8-164124 (Patent Document 1), near-infrared light is irradiated on the back of a finger or a hand, and an imaging element such as a CCD (Charge Coupled Device) is placed on the back side of the inside of the body. It describes a method for observing the spatial distribution of the intensity of transmitted light. Near-infrared light has a small absorption coefficient due to the components that make up the human body, but a large absorption due to hemoglobin, so it can be obtained as a dark image in which blood vessels are light-absorbed.

However, derivation of blood vessel images using near-infrared transmitted light can be used only on relatively thin parts such as fingers and backs of hands. In view of this, there has been proposed a method of obtaining a blood vessel image by irradiating a human body with light and capturing the reflected light after entering the body with an imaging device (for example, Patent Document 1: JP-A-8-164125). Issue gazette).

When using reflected light, it is necessary to capture only light that contains blood vessel information (light that has been reflected once it has entered the human body). However, in general, the intensity of reflected light on the skin surface is overwhelmingly higher than the intensity of reflected light from the inside of the human body, so it is necessary to suppress the latter in some way. For example, JP-A-8-164125 (Patent text) In 1), a liquid is applied to the skin surface to reduce the reflected light directly.

In addition, JP-A-8-164123 (Patent Document 2) irradiates the skin with two types of light having different wavelengths of 4 00 to 6 00 nm and 6 0 to 80 nm, and reflects the internal reflection. A method of obtaining a blood vessel image by using the fact that the former has less light component than the latter and archiving the images obtained by both is described.

In this way, when blood vessel images are obtained using light, there are only a limited number of sites that can be used with the transmission method, and the limited use of force is particularly limited at breast cancer sites. In addition, when the reflection method is used, it takes troublesome work such as applying a liquid to the skin surface in order to suppress the reflected light from the skin surface, multiple light sources, filters, dichroic mirrors, There was a problem that an expensive and complicated device composed of an image analysis mechanism or the like was required.

In addition to the above, for example, JP 2005-21380 (Patent Document 3) and JP 2005-218684 (Patent Document 4) irradiate a subject with light containing a specific wavelength component, 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. In this photoacoustic spectroscopic analysis method, when visible light, near-infrared light, or mid-infrared light having a predetermined wavelength is irradiated on a subject, glucose, hemoglobin, etc. contained in blood in the subject The acoustic wave generated as a result of the specific substance absorbing the energy of the irradiation light is detected, and the concentration of the specific substance is quantitatively measured. As a result, 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. In addition, Special Table 2004-525684 (patent text) Reference 5) describes an apparatus equipped with an applicator for breast cancer examination that examines a tumor site using fluorescence imaging. Further, in Japanese Patent Laid-Open No. 2002-272745 (Patent Document 6), a translucent member is pressed against the breast of a subject, and a ring-shaped irradiating means is provided at the breast base, and imaging is performed through the pressing member. How to do is described.

However, even in the case of photoacoustic spectroscopy, the apparatus configuration is complicated and expensive. In contrast, fluorescence imaging requires administration of a contrast medium. In addition, in the method of irradiating light to the outer periphery of the breast and analyzing the abnormal part from the whole breast image, the optical path difference is large between the image near the nipple and the outer image of the breast. Furthermore, the degree of attenuation of scattered light changes due to changes in the shape of the breast. For this reason, there are problems in the identification of abnormal sites and the accuracy of diagnosis. In order to eliminate or reduce this phenomenon, Japanese Patent Laid-Open No. 2002-272745 (Patent Document 6) presses and flattens the breast by pressing the applicator. However, this increases the size of the apparatus and increases the conventional mammography. With the same discomfort as one. Therefore, none of them are suitable for the purpose of self-examination of breast cancer easily at home for women at risk. Disclosure of the invention

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 found close to the skin, such as breast cancer and skin cancer, which are difficult to identify, can be easily examined at home.

The angiography apparatus of the present invention and the blood vessel distribution analysis system have the following configuration. [1] Probe light emitted from the irradiation unit, which includes 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 configured to prevent the light from directly entering the imaging unit.

[2] 1) A hollow body having an open end that can be in close contact with the 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 the inspection target site received in the hollow body;

3) The angiography apparatus as described in 1 above, further comprising an imaging unit that receives scattered light and / or transmitted light emitted from the buttocks of the inspection target site irradiated with the probe light into the hollow body.

[3] The angiography apparatus according to [2], further including a decompression unit for sucking a part of the examination site 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 applied to the imaging portion by being covered by the inspection target portion received inside the hollow body. 4. The angiography apparatus according to 2 or 3, wherein incidence is prevented.

[5] 1) A hollow body having an open end in a shape capable of being in close contact with a region to be inspected, 2) Provided at or near the edge of the open end and facing the opening in the hollow body or near the region to be inspected Irradiating part that can irradiate probe light toward

3) Spatter emitted from the inside of the examination target irradiated with the probe light toward the hollow body 2. The blood vessel imaging device according to 1 above, further including an imaging unit that receives turbulent light and Z or transmitted light.

[6] The probe light emitting portion of the irradiating portion is provided at the edge of the opening end, and is covered with the inspection target portion that is in close contact with the hollow body opening portion, thereby allowing the probe light or its reflected light to the imaging portion. 6. The blood vessel photographing apparatus according to 5 above, wherein direct incidence of light 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 blood vessel photographing 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 site to be examined is skin and / or subcutaneous tissue.

[1 1] 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 shooting position is specified by measuring the distance and angle from multiple reference positions. 15. The angiography apparatus according to 14,

[16] The angiography apparatus according to 14, wherein the imaging position is specified by measuring a movement direction and a movement amount from the reference position.

[1 7] The angiography apparatus according to 14, wherein the imaging position is specified by analyzing the 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 a storage device that stores image data.

[20] The image data stored in the storage device includes reference data for the normal part and reference data for the abnormal part. By comparing the captured image with the reference data, an abnormality in the blood vessel image in the captured image is detected. 20. The apparatus for diagnosing vascular abnormalities as described in 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, wherein the angiography apparatus or vascular abnormality diagnosis apparatus comprises: A vascular abnormality diagnosis system that analyzes acquired data to determine vascular abnormalities.

[22] A blood vessel distribution analyzing apparatus including means for calculating brightness and darkness of an entire image photographed by any of the devices 1 to 18 and comparing the lightness and darkness of each part of the image to determine blood vessel distribution. [2 3] The gray scale value at the position with the largest gray scale value in the captured image is obtained, the average gray scale value in the area is obtained while enlarging the area to include the position, and the gray scale value is changed. 3. The blood vessel distribution analyzing apparatus according to the item 2, wherein the boundary of the region corresponding to the inflection point is determined as the blood vessel distribution region boundary.

[2 4] Of the captured image, divide the part to be analyzed into k areas, obtain the grayscale value of each area, and then reduce the number of divisions while increasing the area of each area. 24. The method according to 23, further including means for determining a distribution of blood vessels based on a change in gray scale value in a corresponding region between steps by repeating this step until k = 1, Blood vessel distribution analysis device.

[2 5] Of the captured images, the part to be analyzed is divided into non-overlapping polygonal areas of equal area, and the grayscale value of each area is obtained. The low and high areas are combined with their adjacent areas to make a large area, and each grayscale value is obtained. This step is repeated, and the distribution of blood vessels is determined based on the change in the grayscale value between steps. 24. The blood vessel distribution analyzing apparatus according to 24, further comprising means for

[2 6] The device according to any one of 19 to 25, which diagnoses the presence / absence of an angiogenesis abnormality site and the degree of progression of an abnormality based on an analysis result of blood vessel distribution.

[2 7] A breast cancer diagnostic apparatus for diagnosing breast cancer by determining vascular abnormalities using the apparatus according to 26.

[2 8] A method for diagnosing breast cancer 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. Breast cancer and skin cancer, which are difficult to identify, can be easily examined at home for tumors that are close to or close to the skin. Brief Description of Drawings

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 of 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 region segmentation by the imaged 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 angiography apparatus of the present invention.

FIG. 8 is a graph showing changes in the average gray scale value as the selected area of the photographed images in FIGS. 6 and 7 is enlarged.

FIG. 9 is a schematic diagram showing an embodiment of the light irradiation unit of the angiography apparatus of the present invention. FIG. 10 (A) is a schematic view showing another embodiment of the angiography apparatus of the present invention, and (B) is a schematic sectional view corresponding to this. FIG. 11 is a schematic diagram showing still another embodiment of the angiography apparatus of the present invention. BEST MODE FOR CARRYING OUT THE INVENTION

The angiography apparatus of the present invention and its blood vessel distribution analysis system 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 Z or transmitted light from the region to be inspected by the probe light. The probe light emitted from the camera is configured not to directly enter the imaging unit.

Specifically, it may include various aspects, but typically, as the first aspect

1) a hollow body having an open end that can be in close contact with the 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 the inspection target site 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 irradiated with the probe light into the hollow body, and further, as a second aspect,

1) A hollow body having an open end shaped so as to be in close contact with the site to be examined,

2) an irradiating unit that is provided at or near the edge of the opening end and that can irradiate probe light toward the inspection target site facing the opening in the hollow body or the vicinity thereof;

3) including the angiography apparatus having an imaging unit that receives scattered light and Z or transmitted light emitted from the inside of the examination target irradiated with the probe light into the hollow body. Mu

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 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 [cylinder (1) ],

2) An irradiating portion (2) provided at or near the edge of the opening end and capable of irradiating probe light toward the inspection target portion received in the cylinder.

3) An imaging unit (3) that accepts scattered light and Z or transmitted light from the inside of the examination target irradiated with the probe light.

As shown in FIG. 2, the first major feature of the angiography apparatus of 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 is taken from its side. By irradiating p, the scattered light and / or transmitted light s from inside the region to be inspected is imaged (Fig. 2 (C)).

For this purpose, the imaging apparatus of the present invention has an open end shaped so as to be in close contact with the region to be inspected, and a part of the region to be inspected when the open end is in close contact with the region to be inspected (20). (21) has a hollow body [cylinder (1)] for receiving the inside thereof. If the part to be inspected is a body part rich in elasticity, the opening end should be shaped so that it can be in close contact with it, and the opening end will be pressed against the part to be inspected so that a part of the part to be inspected will be pushed into it. However, preferably, the inside of the hollow body [tubular body (1)] can be decompressed, and the site to be inspected is drawn into the inside. (Refer to Fig. 2 (B) and (C)).

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 may be spherical (however, having an open end), Any shape such as hemisphere, truncated cone, truncated pyramid may be used. Here, the hollow body is sufficient if it can take the region to be inspected inside, and as long as it has a hollow portion as long as it is provided. As long as the effect is achieved, a pair of opposing rib-like members may be used. However, when the cross-sectional shape of the open end is square, the distance traveled in the region to be inspected differs when the probe light is irradiated from the inner periphery of the open end. Is preferably circular or elliptical, especially circular.

The open 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 ingestion of the inspection target part into the cylinder does not proceed smoothly. In addition, if the opening end is too large, the probe light absorption 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 pipe or the like is pulled out from a part of the cylinder and the other end is connected to the pressure reducing device. . For the decompression device, any means such as a decompression device based on a reciprocating motion of a piston, a rotational motor or an eccentric motor, or a decompression pump based on a cyclone method can be used. A pump is preferred. For self-examination applications, the switch of the decompression device can be attached to the cylinder or the back of the imaging unit (3), which will be described later, and sucked at the desired position while operating. You can do it. In addition, the cylinder, the decompression device, or the pipe connecting them, should not be excessively decompressed, or maintained at a certain level, or the inside of the cylinder could be quickly returned to atmospheric pressure at the end of shooting. A hole valve means that can be opened and closed 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 is preferably made of a material that is easy to process and has a certain pressure resistance, and that at least the inner surface thereof easily absorbs probe light (for example, near infrared rays) described later. In addition, the opening is preferably made of a material that is easy to install the light emitting means described later and has excellent adhesion to the region to be examined (for example, skin). Each part may be composed of a separate material to meet these conditions. The degree of decompression depends on the flexibility of the target part, the diameter of the opening end, etc., but the target part should be pulled into the opening end at least about 2 to 5 mm. For example, when the target site is skin, the pressure may be reduced from atmospheric pressure to about 1 to 100 h Pa. If the pressure becomes higher than this, the subject may feel pain in the decompression area.

The irradiating part (2) is provided at or near the opening edge of the hollow body (1) as shown in FIGS. 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). Probe light has a wavelength that penetrates biological tissue relatively well and is absorbed by blood vessels, particularly hemoglobin, but near infrared light having a wavelength of 700 to 900 nm is relatively On the other hand, hemoglobin in erythrocytes that flow through blood vessels specifically absorbs near infrared light at 8500 nm, so near infrared light in the above wavelength range is preferable. A light-emitting diode is used by combining multiple wavelength ranges. Also good. For example, when hemoglobin binds to oxygen, its absorption characteristics change depending on its state. Therefore, the absorption wavelength of oxygenated hemoglobin (oxyhemoglobin) 850 nm and the absorption wavelength of deoxygenated hemoglobin (deoxyhemoglobin) 76 0 It may be possible to switch the wavelength of the LED light to be irradiated so that both nm can be measured. The probe light may be a normal light beam or a laser beam.

As shown in Fig. 1 and Fig. 2 (A), it is preferable to arrange the LEDs evenly along the entire inner circumference. 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. Also, as mentioned above, when using LEDs in multiple wavelength ranges, you can install them in combination. Further, when the inside of the hollow body (1) is depressurized, the surface Ψ in contact with the target portion is smoothly received as shown in FIG. It may have an inclined shape.

The photographing part (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 the axis. However, if necessary, the probe light scattered and transmitted from the target site may be extracted from 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 row as shown in the above example, but it may be an array that extends in two dimensions.

The imaging unit (3) typically has a transparent partition (eg, glass or polycarbonate plate) and / or optical system (eg, lens) (4), camera holder ( 5) and imaging means (eg, CCD substrate) (6) Mu The transparent plate is provided for the purpose of avoiding the effects of pressure changes in the cylinder, preventing the pressure reduction in the cylinder from being reduced, and limiting contamination by sebum. The optical system (4), the camera holder (5), and the 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 above-mentioned light, and those that are commercially available as CCD camera units 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 portion by performing imaging while sucking the target portion and performing differential processing on the images of the respective 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 site (for example, Only a small amount of information is available from the skin. On the other hand, in the present invention, since the 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 obtained with high efficiency. In particular, it is preferable that the surface of the probe light emitting portion is covered with the target site (becomes in close contact) because reflected light from the surface of the target site does not enter the imaging site as noise.

In the above case, the area or volume of the target site is large, and the probe light does not sufficiently penetrate into the target site, or the light scattered from inside the target site does not have a sufficient amount of light. In some cases, a good image may not be obtained for the center of the image. Is possible. Therefore, the present invention includes an apparatus that acquires not only the entire region to be examined but also a part of the captured image.

The radiographic image data may be input, displayed, or stored in the 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 examined by the angiography apparatus of the present invention is not particularly limited as long as it is an accessible site, but usually the skin of humans or animals, in particular, the hairless or substantially hairless skin surface is preferred. Flexible skin and / or subcutaneous tissue is preferred. It is suitable to be applied to a site rich in subcutaneous fat, for example, the breast and its vicinity, and is particularly suitable for angiography for diagnosis of breast cancer in this respect.

The second embodiment of the device of the present invention is as shown in FIG.

1) A hollow body (1) having an open end that can be closely attached to a region to be examined

2) An irradiating portion provided at or near the edge of the opening end and capable of irradiating the probe light toward the inspection target portion facing the opening in the hollow body or the vicinity thereof (2), 3) irradiated with the probe light And an imaging section (3) for receiving scattered light and Z or transmitted light (indicated by s) emitted from the inside of the inspection target portion into the hollow body.

The major difference from the first aspect is that the imaging light is not taken into the hollow body, and 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. It is.

This aspect is suitable for photographing a blood vessel image at a relatively shallow position as compared to the first aspect. Also, because the target site is not taken into the hollow body, for example, the skin It is suitable for continuous scanning by smoothly scanning the surface of the camera.

In the second embodiment, the position of the irradiation section is not limited, but it is convenient to provide the irradiation section 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, the probe light output can be increased to obtain information up to a deeper part. Thus, in the second aspect. The hollow body may have a function that its wall surface substantially optically shields between the probe light irradiation unit and the imaging unit (light receiving unit). These materials are determined by the wavelength of the probe light, but an example of near-infrared light is salted blue. However, as shown in FIG. 11, by providing the shielding member (2 2) inside the hollow body, it is also possible to provide both the irradiation part (2) and the imaging part (3) in the hollow body. In the case of Fig. 11, it can also be used for the first mode, so it is possible to scan the surface of the target region widely, and if a detailed examination is required, perform aspiration to image a deeper region. is there.

In this second embodiment, particularly when the irradiation part (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 part. It is preferable to make it incident. The force depending on the position where the irradiation part (2) is provided. The irradiation angle 0 (the probe light incident angle on the surface of the target site) is preferably approximately 10 degrees or more, 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 ° or less is preferable, and 60 ° or less is more preferable. Further, a configuration may be adopted in which an irradiation element such as an LED or a plurality of housings that house the LED is arranged in an interlocking manner so that the irradiation angle 0 is variable. In such a configuration, for example, a concentric double ring structure with different diameters is provided, and inner and outer rings are arranged. This can be realized by changing the relative vertical relationship between the inner and outer rings by pivotally supporting the LED or other irradiating elements or multiple housings housing them in the center and near the outer periphery. Either ring position can be operated directly from the outside of the hollow body. For example, an annular member that is rotatably screwed to 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 aspect, 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 of 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 can include a variety of powers The following four types of configurations are included.

(a) Measuring relative position from the reference position.

(b) Measuring the amount of movement from the reference position.

(c) A device that specifies a position based on a photographed image.

(d) A mark or other coordinates are provided on the target part.

The following is a brief description of the case where the operator performs angiography near his / her breast as an example.

In the configuration (a), a reference position is set at the time of shooting, and the relative position from the reference position is measured. This is typically based on the same principle as triangulation. The reference position can be selected arbitrarily. For example, the left and right ends of the pelvis (respectively L point and R point) can be used as the reference position. The camera is connected to these reference positions in some way, and when shooting at a certain point P, the photographer manipulates the distance LP from the point L and the distance RP or ZPLR from the point R. And ZPRL are recorded in association with the captured image. The L and R points are fixed points, and the P point exists on the operator's skin surface. Therefore, 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 imaging device 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 fitting on the waist and two cord feeding devices provided on the belt-like member. When the operator wears the belt, the two cord feeders (Eg ₁ and 0 ₂ ) are 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 that is provided with an opening for feeding the cord and is rotatably supported around the winding shaft. The take-up shaft is urged in the direction in which the cord is pulled in by a winding spring, for example.

When photographing, a cord is pulled out from each reel-like device and connected to the photographing device. Since the opening for feeding the cord can be rotated around the scraping shaft, the opening rotates following the photographing device when the photographing apparatus is moved. Therefore, if the biasing force is set so that sufficient tension is generated in the cord, Since the take-up shaft, the opening, and the photographing device are arranged in a substantially straight line, the angles Z PCiCs and ZP CSC L formed by the photographing devices P and C ₂ respectively correspond to the above-mentioned ZPLR and ZPRL. In addition, the length of each cord and PC ₂ correspond to the aforementioned LP and RP. Angles ZPCiCs and ZPCsCi can be easily calculated from the rotation angle of the opening and the rotation angle of the take-up shaft of the cord, so that it is possible to specify the shooting position by providing a means to measure these rotation angles Become. Here, what is collectively referred to as a cord is a wire, string, chain, or the like that does not adversely affect measurement when sufficient tension is applied, and can be formed of resin, paper, other fibers, metal, etc. .

Examples of configurations using sound, light, radio waves, and the like include, for example, communication means (the same ₁ and ₂ ) equipped with ultrasonic, light, or radio wave irradiation and reception means as described above in the code sending device. Instead of a belt. In this case, the sound part of the imaging apparatus, the force providing a device for detecting the light or radio waves, sound, by providing a device for emitting light or radio waves, each imaging device P Toje and C _2, acoustic, optically histological or electromagnetic coupling, the distance PC e and PC ₂ is readily determined (eg if the distance PC i are obtained be multiplied the speed of sound in the ultrasonic propagation time fired from C i. ). angle

ZPCsCi can also be easily measured by changing the irradiation angle of ultrasonic waves, light or radio waves, and Z or reception angle using a mechanical drive or an array, so it is possible to specify the shooting position.

In both mechanical configurations and configurations using sound, light, radio waves, etc., the approximate shooting position is specified only by the distance P Ci and PC _2, but the angle ZPdC is taken into account when the breasts are raised. ₂ , ZPCsCi is also preferably measured together. The Further, the elevation angle from the skin surface to the imaging device may be measured. You can also wear it near the scapula instead of the belt on your waist.

In the configuration (b), a reference position is set at the time of shooting, and the 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 can be any position, and can be based on physical feature points (positions such as moles) or fixed points (for example, the lower edge between both breasts). It is preferable to record the position. This can also be realized by providing an imaging device in the visible region in the imaging device or providing a character input device so that a visible image can be taken by the imaging device.

In the case of the mechanical type, the ball is typically coupled to the photographing apparatus in a rotatable manner. This can be achieved by sealing the ball in the housing so that a part of it is exposed outside the housing, as seen in the position identification part of the computer mouse, and connecting the housing with the imaging device. The rotation direction and rotation angle of the ball are measured, for example, by 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 onto 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 device (which may be in the hollow body described above or a light receiving unit may be provided separately), and several feature points are identified by a CCD or the like. When the photographic device is moved, these feature points move in the photographic image. By analyzing this, the moving direction and moving distance are measured. Note that the probe light Irradiation, light reception, and position measurement are unitized in an existing optical mouse, and 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 sound waves or electromagnetic waves obliquely, measuring the moving speed by Doppler shift during movement, and integrating this with time. This method can also be used by an optical method if the detection accuracy is high.

The configuration in (c) specifies the position based on the captured image. (C-1) A configuration that captures a visible image at the time of shooting to identify the position. (c-2) It is analyzed at the time of shooting. An example is a configuration that identifies 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 part as a visible image, or the peripheral image may be taken at a wide angle so that the position can be specified.

The configuration of (C-2) is to localize the imaging position by corresponding to the blood vessel in a substantially 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 sticking a sheet or the like that adheres to the skin on which coordinates or the like are drawn. For example, in the case of breast imaging, wear a cup-type bra or the like that has previously drawn the coordinates that can be seen with visible light and the best effort. Shooting is performed by superimposing infrared and visible light on the cup-shaped brassiere and linking the two, making it possible to specify the position of each captured image. As a cup-type bra, etc., if a skin-contact type is used, there will be almost no displacement during shooting. preferable. For parts other than the breast, use the same flat sheet. Alternatively, it is difficult to see on the skin in the visible range, for example, coordinates are drawn with ink that is close to skin color, and infrared imaging and imaging in the wavelength range corresponding to the complementary color of skin color are performed, and the two are linked. Gore. When drawing the coordinates with ink, use the above-mentioned force-type brassiere as a template or paste the coordinates drawn on the transfer sheet on the breast, peel off the sheet and transfer the coordinates onto the breast can do.

When photographing from above a cup-type brassiere or the like, the second aspect is preferred. In the latter case, both the first and second aspects are possible.

The localization means described above may be combined with either the first aspect or the second aspect, but in particular, it is easy to scan a wide area of the target region for imaging. In this case, the blood vessel distribution under the skin of the target site (for example, the breast) can be accurately obtained over a wide range together with the position information while being a simple device with little burden on the operator. For example, multiple frames are shot per second, and the shot image and 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 the scattered light or transmission emitted from the target site. A device that receives light at the photographing unit, particularly a device in which the irradiation unit and the photographing unit are fixed in a certain positional relationship, particularly a small-sized angiographic device is included in the scope of the present invention.

The apparatus of the present invention may further include an apparatus for displaying a captured image. table The captured image is displayed on a display device (CRT, liquid crystal display, etc.), and the operator can view it as a real-time or recorded image.

The present invention also includes a blood vessel distribution diagnostic apparatus including a blood vessel distribution analysis system. The configuration will be described below.

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 for 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 and darkness of the entire image and determining the distribution of blood vessels from the brightness and darkness 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. It is also possible to determine the blood vessel distribution area from local changes in brightness.

The method is not particularly limited, but as an example of a method for determining the blood vessel distribution area from local changes in light and darkness, the most prominent position (position with a large gray scale value in the photographed image. However, in the following, the gray scale value of simply the darkest point may be stored, and the average gray scale value of the enlarged area may be obtained while enlarging the area to include that portion. . For example, draw circles with radius r centered on the darkest point one after another, and find the average grayscale value inside. This allows the average grayscale value to be specified as a function of r for that image. Since r = 0 is the darkest point, the average grayscale value decreases as r increases, but the rate of decrease is low as long as it is in the region where the blood vessel exists. 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, see the change in the rate of decrease of the average grayscale value Thus, the concentration area of the blood vessel distribution can be defined. In this example, the force of expanding the circle drawn around the reference point is taken as an example. The change in the gray scale value is measured two-dimensionally from the reference point in multiple directions, and the gray scale value on each line is calculated. The concentration region of the blood vessel distribution may be defined by looking at the change (for example, the inflection point).

In addition to expanding the region from the highest 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 the blood vessel distribution part from the gray scale value) in the image area are taken, and Similar to, it is possible to estimate the concentration area of the blood vessel distribution by calculating the average gray scale value and its change (for example, the inflection point) while expanding the area.

The above method eliminates errors caused by non-uniformity of probe light distribution due to the inclination of the measurement device and bias in the target part pull-in, etc., by looking at the rate of change rather than the absolute value of the grayscale value. can do.

Also, in the present invention, the portion to be diagnosed in the captured image is more easily divided into k regions, and the gray scale value of each region (the average value in the region, unless otherwise specified) Then, increase the area of each region and reduce the number of divisions to obtain the grayscale value of each region, repeat this step until k = 1, and then the corresponding region between steps The distribution of blood vessels can be determined based on the change in the gray scale value.

In the above method, the unit area (divided individual area) ai in one step becomes a part of the corresponding unit area a _{i + 1 in} the next step. If one scale value _gi , g _{i +1} is g;> g _{i +1} , a brighter region (ie, a region with less blood vessel distribution in the positive image) is captured by expanding the unit region. That is, the blood vessel distribution is sparser for a _{i + 1} than for a _; On the other hand, if _gi <g _{i + 1} , the blood vessel distribution is denser in a _{i + 1} than in a _; By repeating this step until k = l (ie, unit region = whole part to be diagnosed), the density of blood vessel distribution in each part can be determined. In this method, since the density between adjacent regions is determined, an overall error that can occur when the gray scale values of k regions are simply compared (for example, the device pushes the region to be inspected). This avoids the light / dark bias of the entire photographed image that may occur due to the operation, such as the angle at which it is applied. In practice, it is not necessary to identify individual blood vessels in the diagnosis of cancer and the like, and its density is important, and the present invention provides an efficient diagnosis method for cancer and the like.

Here, the smallest unit area (ie, the first set k areas in the above example) should be comparable to the smallest tumor size at which angiogenesis begins. In the present invention, as described above, for example, a circular region can be photographed, and a ring-shaped region other than the central region can be determined. The “part to be diagnosed” refers to a partial region of such a captured image.

Each unit region is not limited in shape, but is preferably divided into polygons of equal area that do not overlap, for example, a triangle, a rectangle, and a hexagon (particularly, a regular triangle, a square, and a regular hexagon). In the case of a square, the simplest way is to cut out the captured image as the largest square inscribed in the part to be diagnosed. Is divided into m squares, the gray scale value of each area is obtained, and the highest and lowest values are recorded (step 0). Next, n squares adjacent to the circumference of the unit area showing the highest and lowest values are added, and the average clay scale value is calculated (first step). Considering the case where the highest and lowest unit areas are located on the edge of a square cut out from the image, the number of squares ni added in the first step is 3≤n≤8. square number n ₃ ... are applied in adjacent, 3 · 5 · 7 ... · ni 2 3 ... ≤ 8 -.. 1 6 - increased by 2 5 ... range. Sequentially add the grayscale values of all the unit areas, find the average value sequentially, and examine the change in the grayscale value between the highest and lowest values.

When looking at the concentration of blood vessels, changes in grayscale values between steps are relatively slow. On the other hand, if the blood vessels are sparsely distributed, the region that does not contain blood vessels is captured between steps, and the change in the sag scale value increases. In addition, by examining the change from the minimum grayscale area as well as the change from the maximum grayscale value area, it is possible to determine the entire captured image independent of light and darkness.

Data analysis for these image analysis, region segmentation, grayscale value calculation, judgment, analysis of each region and / or change over time, and switching between multiple probe light wavelengths, data Such communication can be controlled by a 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, optical, ultrasonic, etc.). However, it may be possible to control suction and release, probe light irradiation, imaging, etc. with a remote control. An example of the configuration diagram of such a system is shown in FIG. In other words, this system has an irradiation unit (2) for irradiating probe light to a hollow body (1) that receives a region to be examined, and an imaging unit (3), and the imaging unit includes an imaging means (6). (1) is connected to the decompression means (8), and these irradiation section (2), decompression means (8), and imaging means (6) are connected to the computer (10) via the control section (12). is doing. 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 be controlled by a computer (not via the control unit (12)). 10) You can also connect to the configuration. 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 it is usually necessary when a doctor or the like performs direct image diagnosis. Display device (9) Display that guides the imaging procedure, or a visualization image of the imaging result, for example, “no abnormality”, “needs specialist diagnosis”, etc., may be displayed. 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-mentioned 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 the 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 apparatus to image the target region, and records the image on an appropriate recording medium, or a communication line such as a telephone line or an optical fiber. Sent to medical institutions or data collection agencies through which doctors diagnose Is possible.

The irradiation unit (2), decompression unit (8), imaging unit (6) and display device (9) automatically irradiate probe light after suction under the control of the computer (10) It is also possible to use a configuration that measures the amount of light and displays the suction status and the appropriateness of the angle with respect to the target part of the device. The imaging means (6) automatically takes images under the control of the computer (10). You may be able to select the best data among them. Further, the computer (10) may include a program for performing an arbitrary image processing step such as superimposing a plurality 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, it is possible to discriminate the presence or absence of angiogenesis due to some cause. For example, in the case of breast cancer, angiogenesis associated with a tumor starts at a diameter of about 2 mm, and can be identified as a concentration of blood vessels of 2 mm or more. Therefore, the device of the present invention is effective as a diagnostic device for breast cancer. It is.

Example

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.) along the inner circumference of 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 Attach and allow near-infrared light to be emitted toward the center of the cylinder. In addition, on the opposite side of the cylinder, CCD force is applied via a partition (glass plate). Mera (XC-E 150, 768 X 494 pixels, manufactured by Soniichi Co., Ltd., mount: C mount, flange back: 17.56 mm, outer dimensions: width 29 mm x height 29 mm x depth 32 mm) was fixed. In addition, a tube with an inner diameter of 3 Omm was passed through the side of the cylinder, and a suction device was attached to the other end so that the inside of the cylinder could be decompressed.

The above device was pressed against the subject's chest and radiographed. The results are shown in Figs. Fig. 6 shows the case where no set is seen in the blood vessel distribution (depopulated distribution), and Fig. 7 shows the case where a set of blood vessels is seen (crowded 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), for the lowest value: [1] → [2] → [3] → [4] → [5] → [6] → [7]), average grayscale value Was calculated.

Figure 8 shows the change of the average sag scale value as the selected area is expanded. The upper graph in Fig. 8 shows a collection with no blood vessel distribution (depopulated distribution in Fig. 6), and the lower graph shows a blood vessel collection (dense distribution in Fig. 7). The average grayscale value in the bright area is indicated by 〇, and the average grayscale value in the dark area is indicated by ·. As shown in this figure, the grayscale value starting from the unit area showing the maximum and minimum values eventually converges to the grayscale value of the entire image. The slower the grayscale value decreases from the unit area where the grayscale value is the highest, to the surrounding area, the more the blood vessel aggregates, the greater the risk that a tumor will be present. 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 used on the outer periphery of a vinyl chloride cylinder that does not transmit light with an outer diameter of 43 mm and a height of 100 mm. Attached at an angle of 45 degrees so that near infrared light can be irradiated. On the opposite side of the cylindrical opening, a CCD camera (XC-E 150, 768 X 494 pixels, manufactured by Soniichi Co., Ltd., mount: C mount, flange back: 17 through a partition (glass plate) 562mm, outer dimensions: width 29 mm x height 29 mm x depth 32 mm).

In the same manner as in Example 1, the above device was pressed against the subject's chest and imaging was performed, and a blood vessel image in the vicinity of the skin could be obtained.

Example 3

A light irradiation / light receiving 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. The image and position information were recorded simultaneously. By mapping this along the location information, a wide range of angiographic images could be obtained.

Comparative Example 1

Except for the configuration according to Fig. 3, we tried to identify the blood vessel image by measuring the reflected light using the same device as in Example 1, but almost all the light input to the CCD camera was reflected from the skin surface. Significant measurements could not be made. Industrial applicability

The angiography apparatus of the present invention can be manufactured at low cost, is easy to downsize and has a simple apparatus configuration, and thus 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 device in which the subject holds the device in his hand and operates it.

Claims

The scope of the claims

1. A probe emitted from the irradiator, equipped with an irradiator that can irradiate probe light toward the region to be inspected and an imaging unit that accepts scattered light and Z or transmitted light from the region to be inspected by the probe light An angiography apparatus configured to prevent light from directly entering an imaging unit.

2.1) A hollow body having an open end that can be brought into 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,

3) The angiography apparatus according to 1 above, further comprising an imaging unit that receives scattered light and light transmitted from the inside of the examination target 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 site into the hollow body.

4. The probe light emitting part of the irradiating part is provided in the hollow body, and the probe light or its reflected light is directly applied to the imaging part by being covered by the inspection object received inside the hollow body. Item 2 or 3 above, where incidence is prevented Angiography device.

5.1) A hollow body having an open end shaped so as to be in close contact with a region to be examined,

2) An irradiating unit that is provided at or near the edge of the opening end, and that can irradiate probe light toward a region to be inspected or its vicinity facing the opening in the hollow body,

3) The angiography apparatus according to 1 above, further comprising an imaging unit that receives scattered light and Z or transmitted light emitted from the inside of the examination target site irradiated with the probe light toward the hollow body.

6. The probe light emitting portion of the irradiating portion is provided at the edge of the opening end, and the imaging portion of the probe light or its reflected light is covered by being covered by the inspection object site in close contact with the hollow body opening. 6. The angiography apparatus as described in 5 above, wherein direct incidence on the light 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 blood vessel imaging device according to 8 above, 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 site to be examined is skin and Z or subcutaneous tissue.

1 1. The angiography apparatus as described in 10 above, wherein the region to be examined is a part of the 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 movement direction and a movement amount from a reference position.

17. The blood vessel photographing apparatus as described in 14 above, wherein the photographing position is specified by analyzing the photographed 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 above, a display device that displays a captured image, and a storage device that stores Z or image data.

2 0. The image data stored in the storage device includes reference data for the normal part and reference data for the abnormal part, and the abnormalities of the blood vessel image in the captured image are determined by comparing the captured image with these reference data. The vascular abnormality diagnosis device according to 19 above.

2 1. 1 to 8, including the angiography apparatus according to any one of 1 to 20 and the angiography diagnosis apparatus according to 1 9 to 20 and a blood vessel distribution analysis apparatus according to any one of the deviations, and acquired by an angiography apparatus or an anomaly diagnosis apparatus. A vascular abnormality diagnosis system that analyzes vascular data to determine vascular abnormality.

2 2. An apparatus for analyzing a vascular distribution, including means for calculating brightness and darkness of the entire surface image taken by any of the devices 1 to 18 and comparing the brightness and darkness of each part of the image to determine the distribution of blood vessels. .

2 3. Obtain the grayscale value at the position with the largest grayscale value in the captured image, enlarge the area to include the position, and then add the average grayscale value in the area. 3. The blood vessel distribution analyzing apparatus according to 22., wherein a blood vessel distribution area boundary is determined based on a Grace scale value or a change thereof.

2 4. Divide the portion of the captured image to be analyzed into k regions, determine the grayscale value of each region, and then reduce the number of divisions while increasing the area of each region. 24. The method according to 23, further including means for obtaining a grayscale value, repeating this step until k = 1, and determining a blood vessel distribution based on a change in the grayscale value in a corresponding region between steps. Blood vessel analysis device. '

2 5. In the captured image, divide the part to be analyzed into polygonal areas of equal area that do not overlap, determine the grayscale value of each area, and then select the area with the lowest grayscale value. Includes a means to determine each vessel's distribution based on the change in grayscale value between steps, making each grayscale value by determining each grayscale value by combining each high region with its adjacent region. 24. The blood vessel distribution analyzer according to 24.

26. The device according to any one of 19 to 25, which diagnoses the presence / absence of an abnormal site of angiogenesis and / or the degree of progression 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 using the apparatus according to 26. 28. A breast cancer diagnostic method using the breast cancer diagnostic apparatus according to 27.