CN101411607A - Device for photographing conjunctiva and sclera of eyeball - Google Patents

Abstract

The present invention provides an eyeball conjunctiva sclera imaging device, which can compensate the unconscious fretting movement of the eyeball and make it possible to photograph the conjunctival sclera blood vessels, blood flow and blood cells. It includes: an optotype watched by the subject, a camera, a light source, an adjustment structure, an image processing part, an unconscious microvibration compensation part and a display. The imaging device must be able to analyze the conjunctival sclera blood vessels, blood flow and blood cell resolution of the eyeball, be able to compensate for the unconscious microvibration of the eyeball, and be able to distinguish at least 1 μm in a square or rectangular imaging area with a side length of 100 μm to 2000 μm. Graphics, capable of shooting more than 200 images per second. The image processing part can identify the conjunctiva of the eyeball and the blood vessel shape of the sclera, and track and process the images captured by the camera tool. The unconscious fretting compensation part of the eyeball removes fretting from the image processed by the image processing tool.

Description

Eye conjunctiva and sclera camera device

technical field

The present invention relates to an eyeball conjunctiva-sclera imaging device for imaging conjunctiva and sclera. In particular, it relates to a conjunctiva-sclera imaging device capable of compensating for involuntary eyeball vibrations and enabling imaging of blood vessels, blood flow, and blood cells in the conjunctiva and sclera.

Background technique

Known methods for measuring capillaries, blood flow, and blood cells in living things include measuring blood flow by observing blood vessels under fingernails, and measuring blood flow by observing the omentum of the eyeball. speed etc. Such as the published patent document 1 of Japan—JP-A 10-276986; patent document 2-JP-A 2000-83916.

Contents of the invention

problem to be solved

Using a device that measures blood vessels and blood flow under the nail, or using the method of observing the retina of the fundus, blood cells cannot be observed because there is not enough resolution. These methods use the Doppler method to measure the flow velocity of the blood flow, so the flow velocity of the blood flow cannot be obtained from the captured image. In the Doppler method, because the diameter of the blood vessels at the site to be measured is very small, it is impossible to measure each blood vessel, and it is difficult to make a one-to-one correspondence between the blood flow velocity and the position of the blood vessel. Therefore, the known methods are not high-precision methods.

The blood vessels in the conjunctiva and sclera are closest to the body surface, and the conjunctiva on the epidermis has high transparency, which is the most ideal place to measure the shape of blood and blood vessels in living organisms without hindrance. However, when the eyeball is fixedly looking at the target, there are often high-frequency micro-vibrations (up to 90HZ). When shooting capillaries and blood cells, if there are such unconscious micro-vibrations, it is impossible to capture clear images. image.

In view of the above actual situation, the present invention provides a conjunctival-scleral imaging device capable of compensating for unconscious microvibration of the eyeball and clearly photographing blood vessels, blood flow and blood cells of the conjunctiva and sclera.

way of solving the problem

In order to achieve the above-mentioned purpose of the present invention, the conjunctiva-sclera imaging device of the present invention needs to possess:

1. The icon to be watched by the subject;

2. Imaging tools that meet the requirements: the resolution should be high enough to distinguish objects below 1 μm, and the shape of blood vessels, blood flow, and blood cells in the conjunctiva and sclera of the eye can be analyzed; there should be at least a square or rectangular imaging area with a side length of 100 μm to 2000 μm ;It can compensate the unconscious small vibration of the eyeball; it can shoot more than 200 images per second;

3. The camera tool and the light source with illumination in its camera area;

4. An adjustment tool that can adjust the camera tool to move within the camera area;

5. An image processing tool that can recognize the conjunctiva of the eyeball and the blood vessel shape of the sclera and track and process the images captured by the camera tool;

6. An eyeball unconscious fretting compensation tool that can eliminate the fretting of the image processed by the image processing tool;

7. There must be an image display tool, which can not only display the image captured by the camera tool, but also the image processed by the image processing tool, and the image compensated by the unconscious fretting compensation tool.

8. A lens sheet tool can be placed between the icon and the eyeball.

In order to take pictures of the various parts of the conjunctiva and sclera of the eyeball in sequence, the icons can be moved in sequence, and the images can be connected in sequence by the image processing tool.

The work of the unconscious microvibration compensation tool is to select one image from the captured images, extract the pattern of the blood vessel shape, and then search for the corresponding pattern in the connected images, detect the movement amount of the blood vessel shape pattern, and then convert each image The vessel shape pattern in is placed in the same position.

In order to distinguish conjunctival blood vessels or scleral blood vessels, the depth of focus method can be used on imaging tools.

In order to track the blood cells inside the blood vessel, the image processing tool can perform image processing on the image captured by the imaging tool.

The light source here can also be illuminated with light of a specific wavelength, and the reflectance or transmittance of the blood vessel or blood can be used to identify the components of the blood vessel or blood.

The light source here can also be illuminated with a laser light source.

Furthermore, a laser analysis sensor can also be installed to detect the wavelength, phase and intensity of the light reflected from the eyeball.

The position of the laser light source is to make the reflection line of the incident angle of the laser beam incident on the eyeball symmetrical and the reflection angle coincide with the visual axis of the imaging tool.

The laser light source can be composed of a point light source or a line light source, which can scan the imaging area. From the sequential images obtained by the imaging tool, the reflected light of the sclera is extracted by the image processing tool and synthesized to generate a reflected light image of the sclera.

In order to add medicine to the eyeball a nozzle can be used.

Invention effect

Using the conjunctiva-sclera imaging device of the present invention, the blood vessels, blood flow and blood cells of the conjunctiva and sclera can be photographed without damaging the eyes, which is an advantage of the present invention. Therefore, blood can be examined in a non-invasive state.

Description of drawings

Fig. 1 is a schematic side view of the first embodiment of the conjunctiva-sclera imaging device of the present invention.

Fig. 2 is a schematic side view of the second embodiment of the conjunctiva-sclera imaging device of the present invention.

Fig. 3 is a schematic plan view of the second embodiment of the conjunctiva-sclera imaging device of the present invention.

Fig. 4 is an illustration of the relationship among the eyeball, the light source and the camera.

Fig. 5 is a diagram showing the relationship of the conjunctiva, sclera and blood vessels and the obtained images.

Fig. 6 is a schematic illustration of the principle of high-speed imaging and synthesizing images with compensation for unintentional micro-vibration while scanning the imaging area with laser light.

Explanation of symbols in the figure: 1 camera; 2 lens; 3 camera device; 4 light source; 5 adjustment mechanism; 6 image processing part; 7 unconscious microvibration compensation part; 8 display; lines; 14 conjunctival vessels; 15 captured images.

Detailed ways

The following are illustrations and descriptions of the best modes for carrying out the invention. Fig. 1 is a schematic side view of the first embodiment of the conjunctiva-sclera imaging device of the present invention.

As shown in Figure 1, the conjunctival sclera imaging device of the present invention is made up of the icon 10 that the person to be measured looks at, the imaging device 3 that is made up of imaging part 1 and lens 2, light source 4, adjusting mechanism 5, image processing part 6, eyeball unconsciousness. The fretting compensation part 7 and the display 8 constitute.

The camera section 1 is a video camera capable of high-speed photography, preferably a high-speed digital video camera. Lens 2 is a high magnification lens. The imaging device 3 will have: sufficient resolution to analyze the blood vessels, blood flow, and blood cells of the conjunctival sclera of the eyeball 11, can compensate the unconscious microvibration of the eyeball 11, and can adjust the range, resolution, and shooting speed of each image. Function. Specifically: within a square or rectangular photography area with a side length of 100μm to 2000μm, it can distinguish graphics below 1μm, and the shooting speed is more than 200 frames per second. For example, a FASTCAM (registered trademark) camera of Photron Co., Ltd. can be used. It can be adjusted to 1000 frames per second and 1 million pixels, so that the size of each pixel is 7 μm (if the lens magnification is 7 times, you can observe 1 μm). Lens 2 can use a separate high-magnification lens, and if necessary, a wide-angle lens that can take pictures of the whole eye can be placed separately, or a zoom lens can be used. In addition, as a prerequisite for photography, it is preferable that the imaging device 3 is aimed at the center of the eyeball. That is to say, it is better for the camera's visual axis to coincide with the normal of the center point of the camera area, because as the direction deviates from the normal direction, the range that cannot be focused will increase. Because the depth of field of a high-magnification lens is very shallow, if the optical axis of the camera deviates too much from the normal of the center of the imaging area, the distance from the surface of the eyeball to the imaging surface of the camera will change, which cannot be included in the depth of field, and the image will become blurred. Therefore, in order to avoid this type of situation, the included angle between the incident angle of the line of sight of the above-mentioned imaging tool and the normal line of the center point of the imaging area is preferably within 3°.

The light source 4 is a light source capable of illuminating the inside of the imaging area. It can be composed of halogen lamps, optical fibers, lenses, etc., and it must be able to illuminate the entire imaging area, such as a beam with a radius of about 3mm. The light source can also use a beam of specific wavelength, and according to the reflectance or transmittance of the blood vessel or blood, the components of the blood vessel or blood can be identified or measured.

The adjustment mechanism 5 is an adjustment mechanism for the imaging position, and it is used to adjust the intersection of the line of sight of the imaging device 3 and the optical axis of the light source 4 in the imaging area where the conjunctiva and sclera intersect. An adjustment table with 2 degrees of freedom, front, rear, left, and right, can be used. Not only can hardware be used for adjustment, but also software can be used for adjustment. That is, the software selects the position of the required camera frame in the entire camera area.

In order to compensate for the involuntary microvibration of the eyeball, it is necessary to prevent the movement of the head, and a head fixation tool that fixes the subject's head can be used. As a specific fixation tool, you can use a combination tool that bites the stick-shaped equipment with the teeth and the plate-shaped equipment that presses the forehead. The head is fixed against rotation to minimize the range of compensation (movement) for eye movements.

The adjustment mechanism can also be constituted by a driver capable of automatically setting the position of the camera. In addition, it is also possible to take pictures of the corners of the eyes at the same time, and use this position as a reference to compensate for the movement of the head.

The image processing section 6 is constituted by a personal computer, and performs various image processing. That is, the image processing unit 6 performs image processing on the image captured by the imaging device 3 in order to track the blood vessel shape of the conjunctiva and sclera of the eyeball. Specifically, the image processing part 6 first performs preprocessing for removing noise on the obtained image. Generally, the exposure time of high-speed cameras is very short, and a bright enough light source is needed to achieve proper exposure. If a strong light is used to illuminate the eyeball, it will become difficult to take pictures, so use a weaker light source, and the image will be blurred. Generates random noise with high sensitivity. Therefore, noise removal processing, for example, processing with a noise filter is performed. In addition, due to factors such as lens characteristics, the exposure of the surrounding areas of the captured image may sometimes decrease, and the illumination spots of the light source that illuminates the eyeballs may also cause brightness deviation. Therefore, to correct these deviations, vignetting correction or speckle correction can be used. This kind of correction can be made by taking a picture of the white paper in advance, and then correcting it by comparing the image of the eyeball.

The image processing section 6 does not need to use the instantaneous image. Specifically, if there is a big difference between the images obtained sequentially, the images during this period can be ignored. It is also possible to remove the effects of eyelids, eyelashes, shadows, etc. from the image.

The icon 10 can be moved to intentionally turn the eyeballs, and various parts of the conjunctiva and sclera can be photographed sequentially, and these images can be connected together through the image processing part 6 to obtain images in a larger range.

The image after the specified processing by the image processing part 6 is then compensated by the eyeball unconscious fretting compensation part 7 to generate an image without unconscious fretting. The blood vessels of the conjunctiva and sclera were observed in a static state. The unconscious fretting compensation part 7 can be composed of a personal computer, and can share a computer with the image processing part.

The method of unconscious micro-vibration compensation is that the unconscious micro-vibration compensation part 7 compares two consecutive images of sequentially captured images using the area matching method. That is, select the specified area in the previous image and find the same area in the next image. The conjunctiva of the eyeball and the blood vessel shape of the sclera can be used as the designated area. The conjunctiva-sclera imaging device of the present invention performs imaging under the condition of compensating for the involuntary microvibration of the eyeball, so the shape of blood vessels of the conjunctiva and sclera can be captured. Therefore, the part where the blood vessels are densely distributed can be used as the designated area of the area matching method. Take out the specified area, and use the area matching method to search for the matching area on the next image.

The area matching method has been widely used as a pattern recognition method, and the observed pattern can be judged by comparing the coincidence of the ideal pattern and the observed pattern. In the present invention, the area matching method is used for two consecutive images, and the movement amount of the same pattern is compensated in units of pixels. There are generally two types of region matching methods: template matching method and construction matching method. The template matching method is to overlap the reference pattern and the observed pattern, and compare each pixel to determine the similarity. The construction matching method is to extract feature points from the reference pattern and the observed pattern, and determine the similarity by comparing the positional relationship of the feature points. The conjunctiva-sclera imaging device of the present invention can use any matching method, but because there are few edge parts in the image, it is difficult to extract clear features, so the template matching method is generally used. Among the template matching methods, matching methods such as sequential similarity detection method and least square method are widely used. Because the eyeball itself only has parallel motion and rotary motion, it is concluded through actual experiments that the sequence similarity detection method is better.

Next, the sequential similarity detection matching method will be described. In the area of the reference image, we select a part of the image (M _T × N _T pixels) as the reference image T(i, j), and then take the same size (M _I × N _I pixels) in the area of the image to be explored ) of the exploration window I(i, j). That is to say, the reference image is a selected part of the reference image, and the image in the search window is the observed image. In this way, the comparison value between the search window and the reference image in the reference image is D(u, v), which is obtained by the following equation.

$\mathrm{D.}(u,v)={\mathrm{\Σ}}_{i=0}^{m_T-1}{\mathrm{\Σ}}_{j=0}^{N_T-1}|I(i+u,j+v)-T(i,j)|$ Formula 1

In the search area of the observed image, (u, v) when the minimum D(u, v) is obtained is (u _min , v _min ), which is represented by the following formula.

$\mathrm{D.}(u_{\min },v_{\min })=\underset{0\≤i\≤m_I-m_T+\mathrm{1,0}\≤j\≤N_I-N_T+1}{\min }\left(\mathrm{D.}(i,j)\right)$ Formula 2

The position of the exploration window given by the above formula is most similar to the reference image. That is to say, the amount of movement between the reference image and the observed image relative to the eyeball is (u _min , v _min ).

However, the sequential similarity detection and matching method can only detect the parallel movement of the reference image in the detected image, and cannot detect the three-dimensional deformation in the detected image area, and can only detect the two degrees of freedom of the eyeball in the rotational movement. Although there is no problem in this way, if the matching method of the least square method is used instead of the sequential similarity detection method, the 3-degree-of-freedom rotation of the eyeball can be detected, and the three-dimensional deformation can be found.

As described above, detecting the position of the search window in each successive image means detecting the movement amount of the blood vessel shape figure, and then moving the position of each image so that the search window overlaps. In this way, the involuntary vibrations of the eyeball are compensated, so that the shape of the blood vessels seems to be at rest. Using this continuous image that compensates for unconscious fretting, it is possible to perform various analyzes on the conjunctiva of the eyeball and the blood vessels of the sclera.

The display 8 is used to display these compensated images. In addition, if necessary, the display 8 can also be connected with the imaging part 1 or the image processing part 6, and the obtained image or the processed image can be checked by naked eyes.

The method for imaging the eyeball by using the above-mentioned conjunctival-sclera imaging device will be described in detail below. As a prerequisite for taking pictures, it is better to align the camera device 3 at the center of the eyeball, and adjust the shooting area through the adjustment mechanism 5 to align with the center of the eyeball. In order to adjust the position of the camera 3 , the images obtained from the camera 3 can be displayed on the display 8 in real time. Of course, real-time display does not require high-speed camera, and normal camera (30 frames per second) is sufficient.

The camera 1 used in the conjunctiva-sclera imaging device of the present invention can take pictures at a high speed of 1000 frames per second, and the size of each pixel is 7 μm. Moreover, the magnification ratio of the lens 2 is 5-60 times. The images obtained by the imaging device 3 are stored on the personal computer at any time. If necessary, memory device can also be set on camera device 3, and image is saved on the computer after waiting for the camera to finish.

In order to fix the subject's head, press the forehead with the head fixation tool 12, and let the teeth bite the stick-shaped fixation tool. Furthermore, in order to suppress the rotation of the eyeballs, the subject is asked to watch the icon 10 . Then the imaging device 3 of the high-magnification high-speed camera is set to the usual frame rate (for example, below 30 frames/second), and the brightness of the light source 4 is reduced to irradiate the conjunctiva and sclera of the eyeball. If necessary, a wide-angle lens can also be used to take pictures of the eyeball, and the image is displayed on the display 8, and the position of the camera 3 is adjusted by the adjusting device 5 while confirming the image. Then, change to a high-magnification lens and adjust the focus position while checking the image. In addition, the depth of focus can be used to distinguish between conjunctival and scleral vessels. That is to say, because the depth of field is very shallow, you can choose to adjust the focus position so that the focus is on conjunctival vessels or on scleral vessels. Next, in order to obtain good images even at high-speed imaging, the brightness of the light source is increased. However, the brightness of the light source should be kept at a level that does not hurt the eyeball. It is only in this state that high-speed video recording is started, and then the images are sequentially saved to the computer.

Next, by the image processing section 6, one image is taken out of the stored images and designated as a reference image. Preprocess this frame of image, remove noise, perform vignetting correction, spot correction, etc. Through the unconscious microvibration compensation part 7, feature points are extracted from the preprocessed image. Find out the conjunctiva of the eyeball and the part where the blood vessels of the sclera are densely distributed, and take out a window surrounding this part as a reference image.

Next, do the same preprocessing for the next image, and use sequential similarity detection and matching method to compare and detect the position of the search window corresponding to the reference image of the reference image in each image. Then, the positions of the respective images are shifted so that the positions of the corresponding search windows overlap, and an image in which eye movement is compensated is generated.

The blood vessel images of the conjunctiva and sclera generated as described above are very clear images that compensate for the involuntary fretting of the eyeball. Therefore, various analyzes of blood vessels, blood flow, and blood cells can be performed using these images. For example, it is possible to specify a blood vessel from an image, measure the diameter of the blood vessel, and measure the thickness of the blood vessel wall. Because each red blood cell can be distinguished and the amount of movement between each image can be calculated, the red blood cell can be tracked and the speed of movement can be detected. The number of red blood cells in capillaries can be calculated, and the number of red blood cells per unit blood volume can be judged from the flow rate of capillaries. Because individual red blood cells can be resolved, oxygen saturation can be measured through the spectroscopic image. White blood cells can also be detected, and the number ratio of white blood cells to red blood cells can be calculated. In addition, platelets can also be distinguished. The plasma part can be photographed and the components of the plasma can be analyzed.

Then, if it is necessary to add medicine to the eyeball, use a nozzle, and you can observe the blood changes before and after the medicine is sprayed on the surface of the eyeball. If necessary, a fluorescent substance or dyeing substance can be injected into the blood vessel, so that blood and blood vessels can be photographed more clearly.

In addition, information in the depth direction can be obtained by using the depth of focus, and a three-dimensional image of the conjunctiva and sclera can be generated through synthesis.

In the above illustrations, the imaging device is directly aimed at the eyeball as the imaging object. This method is not limited in the present invention, and the description is as follows: the position of the imaging device can be set at any place, and the eyeball is indirectly photographed. Exactly, a mirror is placed between the camera device and the eyeball, the sight line of the camera device is bent by the mirror, and the camera device can be placed on a position that does not block the eyeball line of sight. When the camera is directly aimed at the eyeball, due to the size of the camera itself, it may block the sight of the eyeball and narrow the field of vision. However, compared with the above-mentioned use of mirrors to avoid the problem of blocking the field of view, such problems can also be avoided by changing the camera itself.

Between the eyeball and the camera, an optical fiber can also be set to replace the mirror, so that the camera can take pictures of the eye from any position. When using a mirror, the position of the camera is determined by the position of the eyeball and the focal length of the lens, and the total distance from the eyeball to the camera cannot be changed. However, if an optical fiber is used, the total distance can be set arbitrarily, and the distance between the camera and the eye can be adjusted, so the camera can be installed at any position.

In order to change the distance between the icon placement position and the eyeball perception, a lens sheet can be placed between the icon and the eyeball. Also, in order to make the two eyes seem to see different icons, a lens sheet may be placed between the icon and the eyes. When trying to miniaturize the conjunctival sclera imaging device, it is impossible to put the icon at a far position. When the icon is placed a few centimeters away from the glasses, the testee will be very tired because the icon is very close. In this case, a lens can be placed between the icon and the eyeball, so that even a close-up icon can be easily gazed at. In order to make the icon look far away, different icons can be given to the two eyes, and lens sheets can be used to eliminate the contradiction between vision and the focal distance of the lens of the eyeball.

Next, a second embodiment of the conjunctival-scleral imaging device of the present invention will be described. Fig. 2 is a schematic side view for explaining a second embodiment of the conjunctival-scleral imaging device of the present invention. Fig. 3 is a schematic plan view of the second embodiment. In the figure, parts with the same symbols as those in FIG. 1 are the same devices, so no further description will be given. As shown in Figure 2, the conjunctival sclera imaging device of the present invention is the same as the first embodiment, the icon 10 watched by the subject, the imaging device 3 made up of the camera 1, the lens 2, the light source 4 ', the adjustment mechanism 5, An image processing part 6, an eyeball unconscious fretting compensation part 7 and a display 8 are formed.

The difference between the second embodiment and the first embodiment is that the light source 4' is composed of a laser light source. The laser light source is a point light source or a line light source, and the shape of the irradiation to the imaging part is a point or a line, which can scan the imaging area. If it is a line light source, the illumination shape is a line, and its length is expected to exceed the length of the imaging area. Whether it is a point light source or a line light source, the width of the illuminated shape is narrower. However, the width of the imaging element receiving light in the imaging device is preferably 2 pixels or more. And, as shown in Figure 4, the light source 4', the incident angle of the light source to the eyeball and the line-of-sight angle of the imaging device 3, should be placed on the normal symmetrical position of the eyeball. That is to say, for the normal line of the eyeball, the principle of specular reflection is applied, and the camera device should be placed at the position of the same reflection angle as the incident angle of the light source to take pictures.

FIG. 4 is a diagram illustrating the imaging principle using specular reflection, and is a diagram for explaining the relationship among the eyeball, the light source, and the imaging device. The imaging device 3 is placed on the opposite side of the eyeball normal 13 to the light source, and the imaging angle of the imaging device 3 is the same as the incident angle of the light source 4'. This captures the strongest reflected light. As an example, the line of sight of the imaging device 3 and the optical axis of the laser light source 4' (when it is a line light source, the center of the irradiation shape) are arranged on the same horizontal plane, and the light source and the imaging device are placed symmetrically according to specular reflection. Then, the field of view of the camera 3 is adjusted to align with the center of the eyeball. If the light source 4' uses a line light source, when the surface of the conjunctiva and sclera of the eyeball is irradiated, a linear light image will appear.

FIG. 5 illustrates the relationship among conjunctiva, sclera, and blood vessels, and a captured image 15 . As shown in the figure, the laser light is reflected by the surface of the conjunctiva and the surface of the sclera, and two lines are captured by the camera. If conjunctival blood vessels 14 are present, the blood vessels also reflect the laser light. That is to say, part of the laser light is reflected by the surface of the blood vessel, and the other part is absorbed by the blood vessel and passed through, and reflected by the surface of the sclera. Because the blood vessel is cylindrical, a very small part of the reflected light of the blood vessel is captured as specular reflection light, and most of it is captured as diffuse reflection light, so the non-specular reflection light is very weak. Then, for the scleral reflected light, the part without blood vessels forms specular reflection light, but part of the light passing through the blood vessels is absorbed by the blood vessels, and the reflected light becomes weaker. As shown in the image in Figure 5, the line on the left of the two straight lines in the image is the reflected light on the surface of the conjunctiva, the straight line on the right is the reflected light on the surface of the sclera, and the line between them is the reflected light on the surface of the blood vessel. The reflected light on the surface of the conjunctiva is uniform and bright, while the reflected light on the surface of the sclera is weaker after passing through blood vessels, and part of the light is darker. The reflected light on the surface of the blood vessel is weakened because the blood vessel is cylindrical. In this way, since the presence or absence of blood vessels will change the reflected light on the surface of the sclera, while scanning the imaging area with laser light, high-speed imaging synthesizes an image that compensates for involuntary microvibration, showing the state of blood vessels or blood cells. In addition, as long as the laser beam scans the entire imaging area at a speed of less than 10ms, it is sufficient to compensate for involuntary microvibration. If multiple laser light rays are used to scan at the same time, the scanning speed can be made faster. In addition, the image 15 obtained by using a light source such as a halogen lamp in the first embodiment in addition to the laser beam can be compensated for involuntary fretting like the first embodiment.

Fig. 6 illustrates the principle of high-speed imaging and synthesizing an image compensating for unintentional micro-vibration while scanning the imaging area with a laser light source. Fig. 6(a)-Fig. 6(d) are the process of scanning the image of the imaging part from left to right. The obtained images are shown in Fig. 6(a')-Fig. 6(d'), and the result of combining the reflected images is shown in Fig. 6(e). From Figure 6(e), we know that the reflected light of the conjunctiva is basically consistent, and a uniform and bright image is generated after synthesis. Furthermore, since most of the reflected light of blood vessels is diffuse reflected light, the composite image is dark and unstable. As for the reflected light of the sclera, for the same blood vessel, there are both light reflected after passing through the blood vessel and light transmitted through the blood vessel after reflection. Therefore, two images of the reflected image of the blood vessel and the transmitted image can be obtained from the reflected image of the sclera. That is to say, scan the imaging area with a line light source, extract the reflected light of the sclera from each image obtained by the imaging device, synthesize the reflected light image of the sclera, and obtain the blood vessel image of the reflected light and the transmitted light. In addition, only one of blood vessel images of reflected light or transmitted light may be extracted by image processing. Depending on the distance between the blood vessel and the sclera and the position of the incident angle of the laser light, the reflected image and the transmitted image of the same blood vessel may overlap. In this case, the relationship between the two can be distinguished by image processing, and another blood vessel can be selected for observation.

The blood vessel image obtained by the above method can also be analyzed in various ways for blood vessels, blood flow and blood cells by using the same method as that of the first embodiment. The above examples only illustrate the use of line light sources. Furthermore, when using a line light source, multiple line light sources can also be used to scan, for example, two laser line light sources are used to scan, one image needs to be captured, each of the two lines scans half of the area, and the speed can be doubled. Therefore, as long as multiple line light sources are used to scan beyond the distance of the two radiations of conjunctival reflected light and sclera reflected light, imaging can be performed more efficiently. If a point light source is used, the entire imaging area can also be scanned in the same way, which will not be described here.

In addition, the eyeball is irradiated with a laser light source, and a laser analysis sensor that detects the wavelength, phase, and intensity of the reflected light from the eyeball can be installed to analyze each tissue. In addition, a spectrometer can also be used for the analysis of reflected light.

In addition, the conjunctiva-sclera imaging device of the present invention is not limited to the above examples, and various changes are allowed as long as they do not deviate from the gist of the present invention.

Claims (12)

1. A conjunctiva-sclera camera device for taking pictures of the conjunctiva and sclera of the eyeball, characterized in that it comprises the following devices: The icon to be watched by the subject to be measured; An imaging tool that meets the following requirements: its resolution can analyze the blood vessels, blood flow and blood cells on the conjunctiva and sclera of the eyeball, and it can compensate for the unconscious microvibration of the eyeball. The resolution is so high that it can resolve below 1 μm, and can shoot more than 200 frames per second; A light source that needs to be illuminated in the imaging area of the above-mentioned imaging tool; An adjustment tool for adjusting the position of the above-mentioned imaging tool within the imaging area; An image processing tool capable of distinguishing and tracking the shape of the blood vessels of the conjunctiva and sclera of the eyeball, and performing image processing on the images captured by the above-mentioned imaging tool; Unintentional fretting compensation tools capable of eliminating fretting from images processed by image processing tools; A display tool that can display the image captured by the above imaging tool, or the image processed by the above image processing tool, or the image compensated by the above unconscious fretting compensation tool. 2. The eyeball conjunctiva and sclera imaging device according to claim 1, wherein a lens sheet is placed between the icon and the eyeball. 3. The eyeball conjunctiva and sclera imaging device according to claim 1 or 2, characterized in that, in order to sequentially take pictures of the various positions of the conjunctiva and sclera of the eyeball, the above-mentioned icons are sequentially moved, and the images are sequentially moved by the above-mentioned image processing tool. The obtained images are concatenated and combined. 4. The eyeball conjunctiva and sclera imaging device according to any one of claims 1 to 3, wherein the above-mentioned unconscious microvibration compensation tool can extract the shape of the blood vessel from one frame of the image obtained by imaging. Pattern, search for the corresponding pattern in the next images, measure the movement of the blood vessel shape pattern, and then place the blood vessel shape in each image at the same position. 5. The eyeball conjunctiva and sclera imaging device according to any one of claims 1 to 4, characterized in that the above-mentioned imaging tool can use depth of focus in order to distinguish between conjunctival vessels and scleral vessels for photographing. 6. The eyeball conjunctival sclera imaging device according to any one of claims 1 to 5, characterized in that, the above-mentioned image processing tool, in order to track the blood cells inside the blood vessel, performs image processing for tracking blood cells on the image captured by the imaging tool . 7. The eyeball conjunctiva and sclera imaging device according to any one of claims 1 to 6, characterized in that the above-mentioned light source is illuminated with light of a specific wavelength, and the reflectance or transmittance of blood vessels or blood is used to identify blood vessels Or the composition of blood. 8. The eyeball conjunctiva and sclera imaging device according to any one of claims 1 to 7, wherein the above-mentioned light source is composed of a laser light source. 9. The eyeball conjunctiva and sclera imaging device according to claim 8, further comprising a laser analysis sensor for detecting the wavelength, phase and intensity of the reflected light from the eyeball. 10. The eyeball conjunctiva-sclera imaging device according to claim 8 or 9, characterized in that, the above-mentioned imaging device is placed at a reflection angle position that is symmetrical to the incident angle of the eyeball light source. 11. The eyeball conjunctival sclera imaging device according to claim 10, characterized in that, the above-mentioned light source is composed of a point light source or a line light source to form a scanning imaging area, and the above-mentioned image processing tool is from the sequential images captured by the above-mentioned imaging tool, The images are taken out according to the reflected light of the sclera, and then synthesized to generate the reflected light image of the sclera. 12. The eyeball conjunctiva and sclera imaging device according to any one of claims 1 to 11, wherein a nozzle is used to add medicine to the eyeball.

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