CN202069572U - Optical imaging equipment applied on skins - Google Patents
Optical imaging equipment applied on skins Download PDFInfo
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- CN202069572U CN202069572U CN2011200472146U CN201120047214U CN202069572U CN 202069572 U CN202069572 U CN 202069572U CN 2011200472146 U CN2011200472146 U CN 2011200472146U CN 201120047214 U CN201120047214 U CN 201120047214U CN 202069572 U CN202069572 U CN 202069572U
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Abstract
Optical imaging equipment applied on skins comprises an optical imaging device and an external analysis module, wherein the external analysis module can carry out calculation and analysis on the images of target regions, obtained from the optical imaging device; the optical imaging device comprises an image capturing unit, a lighting unit and a polarizing unit; the image capturing unit can respectively capture sharp images magnified optically by one time and ten times with distortion less than 1 percent; the lighting unit can provide sufficient and evenly-distributed light for the working region of the equipment; and the polarizing unit can remove light reflected by the surface of the skin and irradiated by a lighting source when images are captured, thus decreasing image noises and improving image analysis accuracy rate.
Description
Technical Field
The utility model relates to an optical imaging equipment especially relates to an optical imaging equipment who detects skin tissue.
Background
According to the world health organization's statistics, there are currently about two to three million new skin cancer diseases worldwide per year. As the ozone layer is destroyed, the protective filtering function of the atmosphere is weakened and more solar ultraviolet rays are radiated to the earth surface. Every 10% reduction in the ozone layer is expected to result in 300,000 more skin cancers. Skin cancers (such as melanoma) are often formed by uncontrolled, abnormal proliferation of pigment cells within skin tissue. The most effective treatment for this cancer should be performed when abnormal growth of pigment cells is still less than 1 mm in the skin layer. As the global incidence of skin cancer has increased, the market demand for early and more effective detection of this disease has been stimulated.
Currently, most dermatologists make preliminary evaluations of skin cancer by visual judgment only, which is subjective and has low accuracy with a diagnosis failure rate as high as 40%. When there is a suspected skin cancer condition, a biopsy of the skin tissue is taken to confirm the presence of cancer cells. Such biopsies are not only invasive with some risk, but also leave scars, long examination procedures and expensive laboratory tests. The market is lacking a comprehensive portable tool that can detect skin tissue for potential skin cancer so that suspected cases of skin cancer can be more accurately assessed prior to taking a biopsy.
SUMMERY OF THE UTILITY MODEL
The to-be-solved technical problem of the present invention is to provide a portable device capable of more accurately acquiring and analyzing information on the skin, thereby evaluating suspected cases related to skin cancer.
In order to solve the above technical problem, the utility model provides an optical imaging device, it includes: the system comprises an optical imaging device and an external analysis module, wherein the external analysis module can perform calculation analysis on an image of a target area obtained from the optical imaging device according to the ABCD rule so as to accurately evaluate whether the skin cancer is a suspected case.
The optical imaging device comprises an illumination unit, a polarization unit and an image capturing unit; wherein: the lighting unit comprises a light source, wherein the light source provides light rays for an area needing to capture an image; the polarization unit comprises a primary polarizer, a secondary polarizer, a lens polarizer and a polarization converter, wherein the primary polarizer and the secondary polarizer are used for polarizing the light emitted by the light source, the polarization converter is used for switching the primary polarization and the secondary polarization to polarize the light emitted by the light source, and the lens polarizer is used for analyzing and polarizing the light reflected from the area of the required captured image; the image capturing unit comprises a lens, and the light analyzed and polarized by the lens polarizer passes through the lens to form an image; the polarization directions of the main polarizer and the lens polarizer are consistent, and the polarization directions of the secondary polarizer, the main polarizer and the lens polarizer are mutually vertical.
Wherein the lens can be extended and contracted along the optical axis direction of the lens to image images with different magnifications, for example, the image capturing unit can respectively capture 1-time optical magnification and 10-time optical magnification clear images with distortion less than 1%; the lighting unit can provide sufficient and uniformly distributed light for the working area of the device and respectively emit white light, red light with the wavelength of 619nm-624nm, green light with the wavelength of 520nm-540nm or blue light with the wavelength of 460nm-480 nm; the polarization unit eliminates the light reflected by the skin surface irradiated by the illumination light source when the image is captured, reduces image noise and improves the accuracy of image analysis. Therefore, the optical imaging device is compact in structure and convenient to carry, and can clearly image the target area on the skin, so that the suspected skin cancer case can be more accurately evaluated by combining with an external analysis module.
The utility model discloses a can assist the dermatologist more accurately and appraise skin cancer symptom earlier, record and assay skin pathological change tissue's change fast moreover in skin cancer treatment process. The utility model discloses a whole equipment is very portable small and exquisite, no matter in the complete clinic or in the abominable mountain area of environment, doctor or patient can all directly use the device, open optical lighting part back, the skin surface pathological change region of the required appraisal of camera lens alignment, press the shutter after selecting specific shooting mode, then the leading-in external analysis module of image that will shoot, can have a quick preliminary analysis result, when patient can record the symptom data in different periods, the data that the analysis obtained still helps the dermatosis doctor to give the diagnosis result the very first time, and make corresponding diagnosis and treatment.
The final beneficiaries of the utility model comprise dermatologists and general doctors, and the final beneficiaries can refer to special doctors after the preliminary diagnosis is carried out on the suspected skin cancer patients. Besides the use of the utility model for patients with confirmed skin cancer, a large number of patients with suspected skin cancer can benefit.
Drawings
The following further describes the embodiments of the present invention with reference to the drawings:
FIGS. 1a and 1b are perspective views of an optical imaging apparatus;
FIG. 2a is a front view of the optical imaging apparatus;
FIG. 2b is a rear view of the optical imaging device;
FIG. 2c is a right side view of the optical imaging apparatus;
FIG. 2d is a left side view of the optical imaging apparatus;
FIG. 2e is a bottom view of the optical imaging device;
FIG. 2f is a top view of the optical imaging device;
FIG. 3 is a cross-sectional view taken along the line A-A in FIG. 2 a;
FIGS. 4 and 5 are exploded perspective views of the optical imaging device;
FIG. 6 is an exploded side view of the optical imaging device;
FIG. 7 is a distribution diagram of polarizers in a polarizing unit;
FIG. 8 is a schematic view of the polarization directions of respective polarizing plates;
FIG. 9 is a block diagram of an external analysis module.
Detailed Description
The optical imaging apparatus of the present invention is a non-radiative optical imaging apparatus, which includes a portable optical imaging device and an external analysis module, wherein fig. 1a and 1b are three-dimensional views of the optical imaging device; FIGS. 2a to 2f are six-side views of the optical imaging apparatus; FIG. 3 is a cross-sectional view taken along the line A-A in FIG. 2 a; FIGS. 4 and 5 are exploded perspective views of the optical imaging device; fig. 6 is an exploded side view of the optical imaging apparatus. As shown, the optical imaging apparatus includes an image capturing unit 1, an illumination unit 2, and a polarization unit 3.
The image capturing unit 1 is composed of a set of lenses 1a in cooperation with a specially designed lens movable holder 1 b. The image capture unit 1 and battery power supply 5 are located in a cavity between a device top housing 4 and a device bottom housing 6. The lens 1a is designed by using optical design software ZEMAX, 1-time optical amplification and 10-time optical amplification imaging are respectively carried out at different focal lengths, and imaging distortion is smaller than 1%. The external dimension of the lens movable bracket 1b required by zooming is designed according to the dimension of the lens 1a, namely the diameter of the inner hole of the bracket 1b is the same as the diameter of the shell of the lens 1a, so that the lens 1a can be stably fixed on the bracket 1b, and the lens 1a consists of a group of (two pieces of) lenses. The lens movable holder 1b can be extended and retracted along the axial direction of the optical axis 1c of the lens 1a by a distance equal to the difference between 1-fold optical magnification focal length and 10-fold optical magnification focal length of the lens. The expansion and contraction (i.e., lens zooming) of the movable bracket 1b is controlled by a zoom button 1d on the side of the optical imaging device, and the image formed at the longest focal length is about 1-fold optical magnification, and the image formed at the shortest focal length is about 10-fold optical magnification. The captured image can be displayed on the LCD screen 1e in real time. The image capturing unit 1 can capture 1-fold optical magnification and 10-fold optical magnification of a clear image with distortion less than 1%, respectively.
The lighting unit 2 mainly comprises a plurality of lighting sources 2a and an annular heat dissipation bracket 2 b. The illumination light sources 2a are arranged on the annular heat dissipation bracket 2b at equal intervals, and the illumination mode is controlled by an illumination switch 2 c. The lighting source 2a is a multiband spectrum high-brightness LED, wherein each LED is provided with 3 anodes and 3 cathodes, and the LED can respectively emit white light, red light with the wavelength of 619nm-624nm, green light with the wavelength of 520nm-540nm or blue light with the wavelength of 460nm-480nm by connecting different combinations of the anodes and the cathodes. The light sources with the four colors of white, red, green and blue can be respectively used for lighting different skin cancer lesion areas, so that the skin cancer lesion area images are clearer and are easy to diagnose. In one embodiment, the illumination source has four LEDs, arranged perpendicular to each other in a crisscross fashion. As shown in fig. 3, the illumination unit 2 is located in front of the image capturing unit 1 in the direction of the optical axis 1c between the polarization unit 3 and the image capturing unit 1, and the structural axis of the illumination unit 2 is coaxial with the optical axis of the image capturing unit 1. The diameter of the annular heat dissipation bracket 2b is slightly larger than that of the annular lens movable bracket 1b in the image capturing and lifting unit 1, so that the center of the circle of the annular heat dissipation bracket 2b is located on the optical axis 1c of the lens 1a, the lens 1a can penetrate through the annular heat dissipation bracket 2b, and the LED can provide a light source for an image capturing area required by the lens 1a along the circumferential radial direction of the lens 1 a. The distance between the illumination unit 2 and the image capturing unit 1 along the optical axis 1c is calculated by the optical simulation software LightTools, so that the light in the working area of the optical imaging device is sufficient and uniform.
Fig. 7 is a distribution diagram of polarizing plates in a polarizing unit, and fig. 8 is a polarization direction of each polarizing plate. As shown, the polarizing unit 3 is mainly composed of a circular main polarizer 3a, a circular sub polarizer 3b, a circular lens polarizer 3c, and a polarization converter 3 d. The circular main polarizer 3a, the circular sub-polarizer 3b and the circular lens polarizer 3c may be the same linear polarizer and are respectively mounted on the corresponding circular holes of the polarization converter 3 d. The circular primary polarizer 3a and the circular secondary polarizer 3b serve to polarize light emitted from the light source, so that the circular diameter size and radial position distribution thereof are the same as those of the light source. The circular lens polarizer 3c is for polarizing the lens 1a, and has a circular diameter of the same size as that of the lens 1a and is located in front of the lens 1a in the direction of its optical axis 1 c. The circular primary polarizer 3a, the circular secondary polarizer 3b and the circular lens polarizer 3c are located on substantially the same plane perpendicular to the optical axis. Meanwhile, the circular main polarizers 3a, the circular sub polarizers 3b and the circular lens polarizers 3c are located on a circular plane with the optical axis 1c of the lens 1a as a center and the optical axis 1c of the lens 1a to the optical axis of the LED as diameters, and the circular main polarizers 3a and the circular sub polarizers 3b are equidistantly and alternately distributed along the circumference of the circle. Since the circular main polarizers 3a and the circular sub polarizers 3b are operated in different operation modes, the number of circular main polarizers 3a is the same as the number of circular sub polarizers 3b and the number of LEDs of the light source 2a is also the same. For example, the light source LEDs have 4, and the circular primary polarizer 3a and the circular secondary polarizer 3b have 4, respectively. The circular main polarizer 3a and the circular lens polarizer 3c have the same polarization direction, and the circular sub polarizer 3b and the circular main polarizer 3a have the same polarization direction, and similarly, have the same polarization direction as the circular lens polarizer 3 c. The polarization converter 3d can rotate around the optical axis 1c by an angle equal to the angle between the positions where the adjacent circular primary polarizers 3a and the circular secondary polarizers 3b are mounted. Taking the number of LEDs of the illumination light source as an example of 4, the circular primary polarizer 3a and the circular secondary polarizer 3b are each 4, and the rotation angle of the polarization converter 3d is equal to 360/8-45 degrees. By rotating the polarization converter 3d, the LEDs of the illumination source 2a can be made to coincide with the circular primary polarizer 3a or the circular secondary polarizer 3b, respectively. The longitudinal distance of the polarization converter 3d along the axis 1c is the same as the shortest focal length of the lens in the image capturing unit 1 in the 10-fold magnification mode, which is convenient for the user to position. The circular main polarizer 3a and the circular sub polarizer 3b are used for polarizing the light of the light source, and the circular lens polarizer 3c is used for polarizing the light of the lens, so that the light reflected by the skin surface irradiated by the illumination light source when an image is captured is eliminated, image noise is reduced, and the image analysis accuracy is improved.
The portable optical imaging device has the following 3 operation modes:
mode 1: the image capturing unit 1 is in a 1-time magnification state, and the illumination unit 2 is in an off state;
mode 2: the image capturing unit 1 is in a 10-time magnification state, the illuminating unit 2 is in an on state and respectively uses a white light source, a red light source, a green light source or a blue light source, and the polarizing unit 3 uses the circular main polarizer 3a and the circular lens polarizer 3c through the rotating polarization converter 3d, so that the reflection light irradiated to the surface of the skin by the illuminating light source can be reduced, and the image of the surface layer of the skin cancer lesion area can be clearly captured.
Mode 3: the image capturing unit 1 is in a 10-time magnification state, the illuminating unit 2 is in an on state and uses a white, red, green or blue light source respectively, and the polarizing unit 3 uses the circular sub-polarizer 3b and the circular lens polarizer 3c through the rotating polarization converter 3d, so that the reflected light irradiated to the skin surface by the illuminating light source can be completely eliminated, and the image at the deeper layer of the skin cancer lesion region can be captured.
The above 3 modes operate in the following manner:
after determining the skin surface lesion area to be diagnosed, firstly, using mode 1, the user can hold the optical imaging device with hand and place the optical imaging device at a position 1 times the focal length of the target skin tissue, and the optical imaging device can automatically record the 1 st image after pressing the shutter 7.
Then, in mode 2, the user can hold the device in his/her hand, apply the top of the polarization converter 3d to the target skin tissue, select the desired color of the illumination source 2a, and press the shutter 7 to automatically record the 2 nd image.
Finally, in mode 3, the user can hold the device with his hand, apply the top of the polarization converter 3d to the target skin tissue, select the color of the desired illumination source 2a, and press the shutter 7, the device will automatically record the 3 rd image.
Wherein switching is performed between mode 2 and mode 3 by rotating the polarization switch 3 d. When the device is in the mode 2, the LED of the illumination light source 2a is overlapped with the position of the circular primary polarizer 3a, light emitted by the illumination light source 2a is polarized by the circular primary polarizer 3a and then irradiates a skin surface lesion area needing diagnosis, at the moment, the circular secondary polarizer 3b does not work, light rays are reflected by the skin surface and then enter the circular lens polarizer 3c, and after 3c polarization analysis, images of the surface layer of the skin cancer lesion area are obtained at the image capturing unit 1. When the model 3 is used, the LED of the illumination light source 2a coincides with the circular secondary polarizer 3b, the light emitted by the illumination light source 2a is polarized by the circular secondary polarizer 3b and then irradiates the skin surface lesion area to be diagnosed, at this time, the circular primary polarizer 3a does not work, the light is reflected by the skin surface and then enters the circular lens polarizer 3c, and after 3c polarization analysis, the image of the deeper layer of the skin cancer lesion area is obtained at the image capturing unit 1.
As mentioned above, for the same skin surface lesion area, the device automatically records at least 3 images, and these 3 images can be recorded as the disease data of the skin surface lesion area, and at the same time, 1 image (preferably 2 nd image or 3 rd image) can be selected and introduced into the skin cancer disease analysis module.
As shown in FIG. 9, the analysis principle in the skin cancer disease analysis module employs the ABCD detection rule of skin cancer, which has been internationally proven to be an objective and stable diagnostic method for melanoma. A in the ABCD assay rules indicates asymmetry, including asymmetry in melanoma color and shape. B in ABCD detection rules indicates the border, and the degree of irregularity of the melanoma border is detected. C in the ABCD assay rules indicates the color, and melanoma is detected. D in the ABCD assay rules represents diameter, and the diameter size of melanoma is measured. Internationally recognized criteria are established to judge whether the results of the four items of ABCD are normal or not, and the melanoma is comprehensively diagnosed according to the four results to judge whether the melanoma belongs to skin cancer or not.
And the skin cancer disease analysis module analyzes and calculates the data of the graph according to each judgment criterion of the skin cancer disease analysis module according to the method. After the target skin tissue image is imported, the module can automatically calculate and detect the boundary of melanoma in the image, and then a user starts to select different functions to respectively analyze and calculate items in the ABCD rule. Wherein,
a, measurement by a method: after the analysis module calculates the approximate center line of the melanoma in the image, the shape symmetry percentage and the color symmetry percentage of the left part and the right part of the center line are calculated and displayed;
b, measurement by a method: the analysis module calculates the smoothness of the melanoma boundary curve in the image, and calculates and displays whether the boundary curve belongs to a regular curve or not;
c, measurement by a method: the analysis module calculates the color of the melanoma in the image, judges whether the color belongs to white, black, blue gray, red, light brown or dark brown, and calculates and displays the percentage of each color;
d, measurement by a method: the analysis module calculates the diameter of the melanoma in the image, and calculates and displays the numerical value of the diameter;
the analysis module finally gives a summary according to the four calculation results, displays whether the melanoma in the image belongs to skin cancer or not, and automatically generates a diagnosis report for recording.
And the external analysis module carries out rapid analysis and calculation on the captured target skin tissue image according to the ABCD rule to obtain a conclusion whether the target area belongs to skin cancer diseases or not.
Although a specific embodiment of the present invention has been described above, the present invention is not limited thereto. As long as this optical imaging equipment has adopted the structure like this to and this structure reaches portablely and can judge the effect of the suspected case of skin cancer more accurately, all fall into the utility model discloses the protection within range. That is, without departing from the spirit and substance of the present invention, persons skilled in the art can make various equivalent changes and modifications to the present invention, and such changes and modifications are all within the scope of the present invention.
Claims (10)
1. An optical imaging apparatus includes an illumination unit, a polarization unit, and an image capturing unit; wherein:
the lighting unit comprises a light source, wherein the light source provides light rays for an area needing to capture an image;
the polarization unit comprises a primary polarizer, a secondary polarizer, a lens polarizer and a polarization converter, wherein the primary polarizer and the secondary polarizer are used for polarizing the light emitted by the light source, the polarization converter is used for switching the primary polarization and the secondary polarization to polarize the light emitted by the light source, and the lens polarizer is used for analyzing and polarizing the light reflected from the area of the required captured image;
the image capturing unit comprises a lens, and the light analyzed and polarized by the lens polarizer passes through the lens to form an image;
the method is characterized in that: the polarization directions of the main polarizer and the lens polarizer are consistent, and the polarization directions of the secondary polarizer, the main polarizer and the lens polarizer are mutually vertical.
2. The optical imaging arrangement according to claim 1, wherein the lens is capable of being extended and retracted along an optical axis of the lens to image images at different magnifications.
3. The optical imaging arrangement according to claim 1 or 2, wherein the light source is a high brightness LED.
4. The optical imaging arrangement according to claim 3, wherein the illumination unit further comprises a ring-shaped support on which the light sources are uniformly and equidistantly mounted.
5. The optical imaging arrangement according to claim 3, wherein the high brightness LED emits white, red, green or blue light.
6. The optical imaging arrangement according to claim 1 or 2, wherein the primary polarizer, the secondary polarizer and the lens polarizer are located on a circular plane having a diameter from the optical axis of the lens to the optical axis of the light source as a center of the circle.
7. The optical imaging arrangement according to claim 1, wherein the polarization switch is operative to switch the primary polarizer and the secondary polarizer by rotating the polarization switch about the optical axis of the lens by an angle equal to an angle between adjacent primary and secondary polarizers.
8. An optical imaging apparatus for application to the skin, comprising the optical imaging device of any one of claims 1-7 and an external analysis module for performing computational analysis on the image obtained from the optical imaging device.
9. The optical imaging apparatus applied to the skin according to claim 8, wherein the external analysis module analyzes the boundary, shape, color and size of the obtained image and calculates the values of symmetry of shape and color, degree of regularity of boundary curve, percentage of color type and size of diameter according to ABCD rule.
10. The optical imaging apparatus applied to the skin as claimed in claim 8, wherein said obtained image is an image of the skin.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2011200472146U CN202069572U (en) | 2011-02-24 | 2011-02-24 | Optical imaging equipment applied on skins |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2011200472146U CN202069572U (en) | 2011-02-24 | 2011-02-24 | Optical imaging equipment applied on skins |
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| CN202069572U true CN202069572U (en) | 2011-12-14 |
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| CN2011200472146U Expired - Lifetime CN202069572U (en) | 2011-02-24 | 2011-02-24 | Optical imaging equipment applied on skins |
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105030205A (en) * | 2015-08-07 | 2015-11-11 | 深圳可思美科技有限公司 | Handheld optical high-resolution high-power intelligent skin testing analyzer and system and method thereof |
| CN105193381A (en) * | 2014-06-05 | 2015-12-30 | 苏州速迈医疗设备有限公司 | Dermatoscope |
| CN105979853A (en) * | 2013-12-13 | 2016-09-28 | 莱文尼尔研究有限公司 | Medical imaging |
| CN109152531A (en) * | 2016-04-05 | 2019-01-04 | 制定实验室公司 | Medical image system, device and method |
-
2011
- 2011-02-24 CN CN2011200472146U patent/CN202069572U/en not_active Expired - Lifetime
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105979853A (en) * | 2013-12-13 | 2016-09-28 | 莱文尼尔研究有限公司 | Medical imaging |
| CN105193381A (en) * | 2014-06-05 | 2015-12-30 | 苏州速迈医疗设备有限公司 | Dermatoscope |
| CN105030205A (en) * | 2015-08-07 | 2015-11-11 | 深圳可思美科技有限公司 | Handheld optical high-resolution high-power intelligent skin testing analyzer and system and method thereof |
| CN109152531A (en) * | 2016-04-05 | 2019-01-04 | 制定实验室公司 | Medical image system, device and method |
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Inventor after: Zhou Shengyin Inventor after: Su Wenjie Inventor after: Lei Zhixing Inventor after: Li Limin Inventor after: Lu Zhigang Inventor before: Zhou Shengyin Inventor before: Su Wenjie Inventor before: Lei Zhixing Inventor before: Li Limin |
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Free format text: CORRECT: INVENTOR; FROM: ZHOU SHENGYIN SU WENJIE LEI ZHIXING LI LIMIN TO: ZHOU SHENGYIN SU WENJIE LEI ZHIXING LI LIMIN LU ZHIGANG |
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