CN1287735C - Fluorescent image positioning diagnostic instrument for cancers - Google Patents

Abstract

The present invention discloses a fluorescent image positioning diagnostic instrument for cancers. The present invention uses a fluorescent image positioning method to enhance the space resolution so that uncountable points in the image range can be simultaneously detected in one time. The present invention not only can keep the diagnosis rapid, but also can definitely determine the infiltration range of a tumor. Although the range of the tumor is small at the early cancer, the present invention can definitely determine to display the existence of the tumor. The present invention has the advantages of accuracy, direct viewing, simple and convenient operation method, etc. The present invention not only can be used for the diagnosis of various cancers in the body or outside the body, but also can be used for the diagnosis in the process of adopting the fluorescein (such as a hematoporphyrin derivative HPD) to be combined with the tumor.

Description

Malignant Tumor Fluorescence Image Localization Diagnostic Instrument

technical field

The invention belongs to the technical field of medical instruments, and relates to a fluorescent image positioning diagnostic instrument for malignant tumors.

Background technique

Existing fluorescent spectroscopic diagnostic instruments for malignant tumors use tumor tissue to generate fluorescence under light excitation of a certain wavelength. Receive the fluorescence of tumor tissue, record its spectrum, and identify the nature of the tumor from the characteristics of the spectrum for diagnosis. For example, the Shanghai Institute of Medical Devices applied for the patent of "Malignant Tumor Fluorescence Diagnostic Apparatus" on April 1, 1995, and Fudan University applied for "A Medical Laser Fluorescence Diagnostic Apparatus for Diagnosing Tumors" on December 24, 1987. patent.

The fluorescence spectrum diagnosis of malignant tumors is carried out by utilizing the different characteristics of the fluorescence produced by human tissues in different bands when excited by the excitation light. In existing studies, it has been found that the intensity of normal human tissues is relatively large at short wavelengths of the spectrum (around 500nm). The malignant tumor has a higher intensity ratio near the wavelength of 630nm. The two patents differ in the style of spectral processing technology, and their common feature is that the excitation light is transmitted to the surface of tumor tissue by the same optical fiber for irradiation. The fluorescence emitted by the tumor tissue after irradiation is collected by another optical fiber to the spectrometer, and after dispersion, it is developed into a spectrum, which is converted into an electrical signal by a photodetector to display the spectrum. A detected spectrum is the spectrum at a certain point on the surface of the lesion tissue. If you want to record the spectra of all positions on the lesion, you need to measure the positions of each point of the lesion. It takes a long time to record the spectra of each point of a lesion of a certain size, which is extremely inconvenient. Especially in the early stage of cancer, the general cancer tissue is extremely small in the lesion, and there is no obvious feature. If the point is not taken correctly, the spectrum of the cancer site will not be detected, resulting in misdiagnosis.

Contents of the invention

The purpose of the present invention is to propose an instrument that adopts the fluorescence image positioning method, can record all the spectral information in the tumor area at the same time, and can determine the nature of the tumor through comparison and identification, so as to perform diagnosis.

The malignant tumor fluorescence image positioning diagnostic instrument designed by the present invention is composed of a tumor tissue illumination and image acquisition system, a lesion observation and tumor fluorescence image acquisition system, an image synthesis and display system, and a synchronous control system. Its structure is shown in Figure 1. Among them, the tumor tissue illumination and image acquisition system is composed of a light source 1, an optical filter 2, a light guide 3, an imaging beam 5, and a focusing lens 4. The optical filter 2 is connected to a synchronous control system 16 and is driven by a synchronous motor. The focusing lens 4 Located at the front end of the imaging beam 5, the upper end of the imaging beam 5 faces the image plane conversion mirror 6 of the focus observation and tumor fluorescence image capture system; the focus observation and tumor fluorescence image capture system consists of an image plane conversion mirror 6, an image channel selector 7, A light baffle 8 with light holes A and B, a synchronous image separator 10, a CCD color camera 9, and a CCD black and white camera 12 and 14 are connected to form. Wherein, the image surface conversion mirror 6 is arranged between the output port of the imaging beam 5 and the image channel selector 7, and the image channel selector 7 is composed of two total reflection mirrors glued together; the light blocking plate 8 is arranged between the image channel selector 7 and the camera Between, its axis of rotation is located at the center of the optical path, one light hole A on the top is aligned with the color camera 9, and the other light hole B is aligned with the synchronous co-position image separator 10; the image separator 10 is composed of a two-color light splitting element C and an image compensation The total reflection mirror D is formed, respectively aiming at the black-and-white cameras 12 and 14, and a short-wave color filter 13 and a long-wave color filter 11 are respectively arranged in the middle. The image synthesis and display system 15 communicates with the cameras 9, 14, and 12 respectively, and synthesizes and displays the images acquired by the cameras. The synchronous control system 16 is composed of a synchronous motor and a control circuit, and is connected with the optical filter 2 and the image channel selector 7, and controls the output of the image from different light holes of the light blocking block to be synchronized with the conversion of the lighting mode.

The working mode of the present invention is as follows:

The light emitted by the light source 1 passes through the optical filter 2 driven by the synchronous motor, and the output light enters the light guide 3 and irradiates the surface of the tumor tissue. The image of the tumor excited by the illumination light is imaged by the short-focus lens 4 in front of the imaging beam 5 on the input end of the imaging beam, and output from the other end of the imaging beam. The image surface conversion lens 6 converts the image output by the imaging fiber to the receiving target surface of the CCD camera placed at the far end, and a series of optical elements between the image surface conversion lens 6 and the CCD camera control the image. The image channel selector 7 is composed of two groups of total reflection mirrors, through its rotation, the image can be output from any light hole in the light baffle 8 with 2 light holes A and B at the back. If the image is output from the aperture A, the image enters the color camera 9, and the image is captured and displayed by the image synthesis display system 15. At this time, what is displayed is the real tumor under full light illumination when the light source does not add a color filter. color image. When the image channel selector 7 is rotated to output through the light hole B, the image is divided into two kinds of images of different colors through the synchronous image distributor 10, the long-wavelength image enters the black-and-white camera 12 through the long-wave filter 11, and the short-wavelength image passes through the band The filter plate 13 that has short wave enters black-and-white camera head 14. However, these two sets of images are fluorescence images excited by the light source 1 and the optical filter 2 on the tumor tissue. These two groups of images are respectively captured and processed by the image synthesis and display system 15 into fluorescent diagnostic images. Based on this image, the nature of the tumor can be clarified. When the image is output from the light hole A or B hole, it is illuminated by different light sources. To realize this transformation, there is a synchronous control system 16 and an image channel selector dial 22 at the corresponding positions of the light hole A and B respectively. Positioning switch to achieve. When the image channel selector dial rotates to make the image channel selector 7 turn to the light hole A, the positioning switch corresponding to the light hole A on the image selector dial outputs a signal to the synchronous control system 16, and the synchronous control system 16 passes The circuit controls the rotation of the synchronous motor of the optical filter 2, so that the color filter is moved away from the optical path, thereby completing full-light illumination, and capturing and displaying color images. When the image channel selector dial 22 turns the image channel selector 7 to the aperture B, the positioning switch corresponding to the aperture B outputs a signal to the synchronous control system 16, and the synchronous motor of the optical filter 2 is reversed. Rotate the direction to move the color filter to the optical path. At this time, the illumination is polarized illumination, and the color-biased illumination shines on the tumor to complete the fluorescence excitation of the tumor tissue. After excitation, the tumor image is output through the light hole B and then enters the synchronous co-position image separator 10 The long-wave spectrum and short-wave spectrum images are captured and processed by the computer and finally displayed, thus completing the fluorescence image diagnosis process.

Description of drawings

Fig. 1 is a schematic diagram of the overall structure of the present invention.

Fig. 2 is a structural diagram of a synchronous motor turntable equipped with an optical filter, wherein Fig. 2(a) is a front view, and Fig. 2(b) is a side view.

Fig. 3 Structural diagram of lesion illumination and image acquisition system.

Figure 4 Schematic diagram of the system structure for lesion observation and tumor fluorescence image capture.

Figure 5 shows the structure and installation diagram of the image plane conversion mirror. Among them, Figure 5(a) is a diagram of the imaging surface of an imaging fiber, Figure 5(b) is a diagram of a 1/2-inch CCD target surface, Figure 5(c) is an image conversion mirror group, and Figure 5(d) is an image plane Schematic diagram of conversion mirror installation.

Figure 6: Image channel selector for positioning and selecting images. Among them, Figure 6(a) shows that the image is output from hole A, and Figure 6(b) shows that the image is output from hole B.

Fig. 7 Diagram of image channel selector dial and light baffle.

Figure 8 Schematic diagram of a synchronous image separator.

Figure 9 is a diagram of the image synthesis display system.

Figure 10 Synchronous controller circuit diagram.

Figure 11 is a schematic diagram of the working principle of the synchronous controller. Wherein, Fig. 11(a) is a forward rotation diagram, and Fig. 11(b) is a reverse diagram.

Numbers in the figure: 1 is the light source, 2 is the optical filter, 3 is the guide beam, 4 is the short-focus lens, 5 is the imaging beam, 6 is the image surface conversion mirror, 7 is the image channel selector, 8 is the light-through The light baffle of the hole, 9 is the color camera, 10 is the synchronous image separator, 11 is the long-wave color filter, 12 is the CCD black and white camera, 13 is the short-wave color filter, 14 is the CCD black and white camera, 15 is the image synthesis display system , 16 is a synchronous control system, 17 is a tumor focus, 18 is a light source limit switch, 19 is a light hole, 20 is a color filter, 21 is a shelf, 22 is an image channel selector dial, and 23 is an image channel The selector is close to the switch, 24 is an image positioning switch, 25 is an image multi-channel capture recorder, 26 is a spectral image processing synthesizer, 27 is a four-grid image display, and 28 is a synchronous motor.

Detailed ways

The specific implementation manner of the present invention will be further introduced below.

In the present invention, the excitation light source 1 of the tumor tissue illumination and image acquisition system can be a light source with a strong output in the range of 400nm-430nm, such as a mercury lamp or other light sources, or it can be composed of an ordinary light source and a semiconductor laser working at 400nm of mixed light sources. The color filter in the optical filter 2 can adopt a short-wave pass color filter below 435nm, which can filter out light with a wavelength above 435nm. The color filter can be installed on the turntable of the optical filter of the synchronous motor, and is located between the entrance of the light guide 3 and the light source 1; the light guide 3 and the imaging beam 5 can use glass optical fibers, and the section of the imaging beam 5 can be 3-6mm2 , such as a 2×2mm arrangement, an arrangement with a diameter of 3mm, and the like. The cross-sectional diameter of the light guide can be 6-10mm. The imaging mirror 4 can be a short-focus lens whose diameter matches that of the imaging beam 5 . The glass optical fibers for the imaging bundle are arranged one-to-one, and their upper ends are aligned with the image plane conversion mirror 6 of the observation and imaging device of the tumor diagnostic instrument; the guiding beam 3 and the imaging beam 5 are made into a coaxial structure, that is, the guiding beam can be Around the imaging beam, as shown in Figure 3.

As an alternative, the imaging beam 5 can also use a trapezoidal self-focusing imaging fiber.

In the present invention, the image plane conversion lens 6 of the lesion observation and tumor fluorescence image capture system enlarges or reduces the front image, and matches with the image receiving element installed in the back. Determined, for example, the diagonal of the 2×2 image plane is 2.8mm, and the diagonal of the 1/2inch target surface received by the CCD is 8mm. If the front and rear images are to match, the image needs to be enlarged by 2.9 times, while There are many ways to magnify images. In order to obtain high-quality image magnification, the system with the structure shown in Figure 5(c) is usually used, which consists of two groups of lenses with different focal lengths. If the image of the front section is on the focal plane of one set of lenses, the image of the back section is on the focal plane of another set of lenses, and its magnification ratio is the ratio of the focal length of the back section lens to the front section lens. Considering factors such as lens dispersion and astigmatism, the lenses generally used are dispersion-compensating cemented lenses. The lens used in the embodiment of the present invention is φ15mm, the focal length of the front lens is f ₁ =15mm; the focal length of the rear lens is f ₂ =45mm. The magnification factor is 3. In order to ensure the stability of the light and that there is enough space to insert other optical elements in front of the CCD camera, the installation method of Figure 5 (d) is adopted to install the front section of the image plane conversion lens in front of the image channel selector 7, and the image plane conversion lens The rear section is placed on the light barrier 8 behind the image channel selector. The distance from the rear segment lens to the CCD target surface is adjustable from 40mm to 50mm.

The image channel selector 7 can be formed by gluing two total reflection mirrors. It is inserted between the image plane conversion mirror 6 and the baffle plate 8 with two fixed light holes. The image channel selector 7 is installed on the rotatable dial 22 . Its image input end is located on the rotation axis of the rotary dial, and a proximity switch 23 is installed on the outer side of the dial corresponding to the image output end. By rotating, the image output end of the image channel selector 7 can be aligned with the light hole A, or through Light hole B (as shown in Figure 6). The angle α between the two light holes on the light blocking plate 8 with two light holes can be arbitrarily selected from 0-180 ° (as shown in Figure 7), and the two light holes in the embodiment of the present invention The included angle between is selected as 120°.

The lesion observation image is obtained from the output of the aperture A by the aperture baffle 8, received by the image camera 9, captured and displayed by a computer. In the embodiment of the present invention, a WATEC217HS color camera with a sensitivity of 1/2 inch and a sensitivity of 0.2 Lux is used.

The above synchronous image separator 10 is composed of two groups of optical elements, wherein C is made of two 45° prisms coated and glued on the inclined surface, the short-wave image can be transmitted, and the long-wave image is reflected by the two-color light splitting element , D is the image bit compensation total reflection prism, as shown in Figure 8. After the spectral image is output from the aperture baffle B and enters the synchronous co-position image separator, the image is separated synchronously by the two-color light-splitting element C. According to the transmission and reflection characteristics of the light-splitting element C, the separated images are respectively long-wave band (reflection) and short-wavelength. However, the long-wavelength image in these two groups of images has undergone a 45° reflection, and the upper and lower sides of the image are inconsistent with the short-wavelength image, forming a positive image and a negative image. In order to keep the two groups of images consistent in terms of bit images, an optical compensation method is adopted in the present invention. In this method, the upside-down long-wavelength image is reflected by the 45° reflection of the image position compensation total reflection prism, and then upside-down is performed again, and the long-wavelength image after the second inversion is in the same position as the short-wavelength image. A consensus was achieved on the image. Finally, the two groups of images enter their respective image channels, the long-wave images enter the long-wave color filter 11 to reach the camera 12 , and the short-wave images enter the short-wave color filter 13 to reach the camera 14 . In this way, the accurate analysis and processing of the fluorescence spectrum at each point of the tumor tissue can be achieved.

In the synchronous and co-located image separator of the present invention, the wavelength of light splitting by the C coating of the two-color light splitting element is 580 nm. That is, the reflectance of wavelengths greater than 580nm is not less than 85%, and the transmittance of wavelengths less than 580nm is not less than 85%. The long-wave color filter used in the embodiment of the present invention has a cut-off wavelength of 600 nm, a long-wave pass color filter, and the short-wave color filter has a cut-off wavelength of 540 nm. The long-wave and short-wave images are obtained by two high-sensitivity black-and-white cameras. The black-and-white camera uses a 1/2inch target surface with a sensitivity of 0.0003Lux.

A kind of transformation, change the technical parameters of the light-splitting wavelength of the two-color spectroscopic element C in the synchronous co-located image separator, the long-wave color filter 11 and the short-wave color filter 13, and the present invention can be used for hematoporin derivative HPD and other Combined with a good fluorescent substance in the malignant tumor, the diagnosis of the spectral image of the malignant tumor after injection, oral administration, or painted on the surface of the tumor.

The image synthesis and display system 15 of the present invention can be composed of an image multi-channel capture recorder 25 , a spectrum image processing synthesizer 26 and a four-grid image display 27 , as shown in FIG. 9 . From the color camera 9 and the long-wave image camera 12, the video signal of the short-wave image camera 14 is input into the image multi-channel capture recorder and then processed in a certain format and stored in the hard disk video recording system, wherein the long-wave spectral image and the short-wave spectral image are output to the spectral image The processing synthesizer obtains the video signal strengths of the corresponding points of the image through screening one by one and divides them.

The image points of J>Q (the value of Q is obtained with the test card) are red. Image points with J≤Q are represented in blue. In the same representation color, the brightness of image points also varies with the difference between J and Q.

The value of Q in the present invention is obtained by the standard test card under certain experimental conditions, which is used to eliminate the impact caused by the discreteness of sensitivity between the cameras of the long-wave spectrum and short-wave spectrum selected above.

浓度。The standard test card of the present invention is made to adopt hematoporin derivative (HPD) former reagent to dilute with distilled water to

concentration.

最后取其各点q₁…n的平均值定为Q。即 $Q=\stackrel{\‾}{q_1}\·\·\·n.$ Use a standard dropper to spread a little bit on standard filter paper. The area is not less than φ20. Dry in the shade and test after 2 hours. Test conditions: A) irradiate with a 405nm semiconductor laser, and the irradiation intensity is 0.002W/cm ² ; B), the distance between the imaging end of the tumor illumination and image acquisition system II and the test card is the shortest (5mm), and the long-wave and short-wave are obtained through the test Filter paper fluorescence image.

Finally, the average value of each point q ₁ ...n is taken as Q. Right now $Q=\stackrel{\&OverBar;}{{\mathrm{<figure-callout\; id="1"\; label="q"\; filenames="C0215102200181.png"\; state="\{\{state\}\}">q</figure-callout>}}_1}\&Center\; Dot;\&Center\; Dot;\&Center\; Dot;\mathrm{no}.$

The four-way grid image display is to display the images recorded by the image multi-channel capture recorder. The I area is the tumor color image for lesion observation, the II area is the tumor fluorescence long-wave image, the III area is the tumor fluorescence short-wave image, and the IV area is Tumor fluorescence image synthesis is the image representation of diagnostic results. In the image, any red area is the site where tumor cells exist.

In the present invention, the synchronous controller system 16 is to control the synchronism between the output of images from different apertures and the illumination mode. Its control circuit is composed of two image positioning switches for capturing different images, two light source limit switches for controlling the transformation of the lighting mode, and a relay for controlling the working state through circuit connection. Its structure is shown in Figure 2, Figure 7 and Figure 10. Among them, the two light source limit switches L and K are arranged on the turntable of the synchronous motor. There are light holes 19, color filters 20 and shelf pieces 21 on the turntable of the synchronous motor, and the limit switches L and K are located on the shelf piece 21. There is a certain included angle (for example, the included angle is 60°) to the center of the turntable on both sides, the light hole 19 and the color filter 20 are respectively located at the center symmetrical positions of the light source limit switches L and K, and the turntable is installed on the synchronous motor. As shown in Figure 2; 2 image positioning switches M and N are respectively arranged on the edge of the image channel selector dial 22 of the instrument, and the dial 22 is provided with two image channel holes A and B, and the image positioning switches M and N correspond to At the position of the channel holes A and B, there is a corresponding angle with the center of the dial (for example, the angle is 120°), (that is, the angle between the center of the channel holes A and B and the center of the dial), as shown in Figure 7 As shown; the contact switches of the four relays J _M , J _N , J _L , J _K installed on the circuit board are connected to the corresponding image positioning switches M, N and light source limit switches L, K, as shown in Figure 10 shows.

In the control circuit, the 220V voltage becomes 12V DC power supply after passing through the transformer P and the rectifying element U. The 12V DC power has four output circuits: ① supply power to the relay J _M coil through the image positioning switch M, ② supply power to the relay through the image positioning switch N J _N coil supplies power, ③ supplies power to the coil of relay J _L through the light source limit switch L, ④ supplies power to the relay J _K coil through the light source limit switch K; there are two bypasses on the switch M, one is by the switch J _M1 It is composed of series connection with J _N4 , and the second is composed of switch J _M6 and J _N6 in series; switch N has a bypass, which is composed of switch J _N1 and J _M4 in series; switch L has a bypass, which is connected by switch J _L1 Composed in series with J _K4 ; there is a bypass on the K switch, which is composed of switches J _K1 and J _L4 in series; the synchronous motor power supply circuit is that one end of the 220V incoming line is connected to the 3 pin of the motor winding II through the capacitor C ₁ , 220V The other end of the incoming line is directly connected to the 4-pin of the motor winding II; the 3-pin circuit of the motor winding II is connected to the 2-pin of the motor winding I through the switch J _M2 and J _L2 , and the other circuit is connected to the motor winding I through the switch J _M5 and J _L5 is connected to pin 1 of motor winding I; pin 4 of motor winding II also has two loops connected to motor winding I: one is connected to pin 1 of motor winding I through capacitor C ₂ , switch J _N5 and J _K5 , and the other One is connected with pin 2 of the motor winding I through switches J _N2 and J _K2 . (Note: Each relay has 6 switching states, which are marked with different numbers. Among them, the numbers marked with 1-3 are normally open switches; the numbers marked with 4-6 are normally closed switches.)

The working principle of this control circuit is as follows: first, it is assumed that the image channel selector 7 is positioned on the M switch, and the turntable 18 with the light hole 19 and the color filter 20 is limited on the L switch. At this time, the relay J _M in the circuit works , J _N does not work, relay J _L works, J _K does not work. That is, the corresponding switches J _M2 , J _N5 , J _L2 , and J _K5 of the relays J _M , J _N , J L , and _{J K} are on, while the switches J _M5 , J _N2 , J _L5 , and J _K2 are off. Pin 3 of synchronous motor winding I is connected to pin 2 of winding II, and pin 4 of winding I is connected to pin 1 of winding II through capacitor C _2. According to the forward connection method of the motor, the motor drives the turntable 1 to rotate clockwise, and the turntable is placed on it. Plate 21 moves away from L and moves in K direction. When the shelf piece 21 leans against the limit switch K, J _L does not work in the circuit, and J _K works, that is, the switches J _M2 , J _N5 , J _L5 , and J _K2 are on, and the switches J _M5 , J _N2 , J _L2 , J _K5 is blocked (see Figure 11(a)). The synchronous motor winding I and winding II are not connected, and the motor stops rotating. At this time, the light hole on the turntable is on the illumination light path, and the A channel on the image channel selector 7 is full light illumination. However, when the dial of the image channel selector 7 is turned to B, J _N works, J _M does not work, and the dial is in the state that J _K works, and J _L does not work. That is, the switches J _M5 , J _N2 , J _L5 , and J _K2 are on, and the switches J _M2 , J _N5 , J _L2 , and J _K5 are off (see Figure 11(b)). Pin 3 of winding I of the synchronous motor is connected with pin 1 of winding II, and pin 4 of winding I is connected with pin 1 of winding II through capacitor _C2 . If the motor is connected in reverse, the motor drives the turntable to rotate counterclockwise. The shelf piece 21 on the turntable moves away from K and moves toward L. Once the shelf piece 4 reaches L, J _L and J _M bounce back to work for J _L , and J _K does not work. Among the contacts of relays J _M , J _N , J _L , and J _K , J _M5 , J _N2 , J _L2 , and J _K5 are connected, while J _M2 , J _N5 , J _L5 , and J _K2 are not connected. The winding I of the synchronous motor is disconnected from the winding II and stops rotating. At this time, the color filter 20 on the turntable just cuts into the illumination light path, and the light source becomes a polarized illumination mode. That is to say, when the image channel is in B, the light source is filtered by the color filter 20. Therefore, the problem of synchronous lighting control in different lighting modes for different image channels is realized. The G connection in Fig. 10 is to solve the automatic start-up problem when the shelf sheet in the turntable does not lean against any switch of the L and K switches, so that it can start to the proper position of the turntable according to the state of the image channel selector positioning switch. To improve the reliability of the control system.

The present invention can adopt the slow speed motor that reversing synchronous motor rotating speed is 10 revolutions/min. Turning 60° is the conversion angle between the filter and the light hole, so that the time for switching between the filter and the light hole in the light path is 1 second.

The lighting synchronous controller designed by the utility model has reliable performance and is easy to control. It provides different lighting modes for tumor image observation and fluorescence image diagnosis, ensures correct analysis, and can avoid damage to instrument parts at the same time.

Claims (8)

1, a kind of malignant tumor fluoroscopic image level diagnosis instrument is characterized in that by tumor tissues illumination and image capturing system, focus observation and tumor fluoroscopic image capturing system, image synthesize and display system, synchronous control system combine; Wherein, tumor tissues illumination and image capturing system by light source (1), optical filter (2), light guide bundles (3), become video beam (5) and short-focus mirror head (4) to form, optical filter (2) is connected with synchronous control system (16), and driven by the syncmotor in the synchronous control system, short-focus mirror head (4) is positioned at into the front end of video beam (5), and the upper end that becomes video beam (5) is facing to the image planes conversion mirror (6) of focus observation with tumor fluoroscopic image capturing system; Focus observe with tumor fluoroscopic image capturing system by image planes change mirror (6), image channel selector (7), have the light barrier (8) of two light holes (A, B), coordination image splitter (10), CCD colour imagery shot (9), CCD black and white photographic head (12,14) connect to form synchronously; Wherein, image planes conversion mirrors (6) are arranged at between the delivery outlet and image channel selector (7) of video beam (5), and image channel selector (7) is made up of 2 completely reflecting mirror gummeds; Light barrier (8) is arranged between image channel selector (7) and the photographic head, its rotating shaft is positioned at the light path center, light hole (A) above the light barrier (8) is aimed at colour imagery shot (9), another light hole (B) synchronism coordination image splitter (10); Image splitter (10) is made of double-colored beam splitter (C) and image position compensation total reflection prism (D), aims at black and white photographic head (12,14) respectively, is respectively equipped with shortwave light filter (13) and long wave light filter (11) in the middle of it; Image synthesizes and display system (15) is communicated with photographic head (9,12,14) respectively, the image that is obtained by photographic head is synthesized, and show; Synchronous control system (16) is made of syncmotor and control circuit, and is connected with image channel selector (7) with optical filter (2), the control figure picture during from the different light holes output of light barrier and the lighting system conversion synchronization carry out.

2, diagnostic apparatus according to claim 1, it is characterized in that the light source that the tumor tissues illumination and light source (1) employing of image capturing system are exported in the 400nm-430nm scope, light filter in the optical filter (2) adopts the following short-pass light filter of 435nm, this light filter is installed on the rotating disk of syncmotor, is positioned between the import and light source (1) of light guide bundles (3); Light guide bundles (3), one-tenth video beam (5) adopt glass optical fiber, and becoming video beam (5) cross section is 3-6mm ², the light guide bundles diameter of section is 6-10mm; The diameter of short-focus mirror head and the diameter coupling that becomes video beam (5); The glass optical fiber that becomes video beam to use is arranged one to one, and its upper end is in alignment with image planes conversion mirror (6); Light guide bundles (3) is made the coaxial configuration form with becoming video beam (5).

3, diagnostic apparatus according to claim 1, the image planes conversion mirrors (6) that it is characterized in that capturing system are made up of the lens that two groups of focal lengths are respectively different focal, wherein, image planes convertible lens prosthomere is placed in the front of image channel selector (7), image planes convertible lens deutomerite is placed on the light barrier (8) of image channel selector (7) back, and image planes convertible lens deutomerite is adjustable at 40-50mm to CCD target surface distance.

4, diagnostic apparatus according to claim 1 is characterized in that image channel selector (7) is formed by 2 completely reflecting mirror gummeds, is inserted between image planes conversion mirror (6) and the light barrier (8); Angle α between last 2 light holes of light barrier (8) is selected arbitrarily at 0-180 °.

5, diagnostic apparatus according to claim 1, it is characterized in that synchronous coordination image splitter (10) compensates completely reflecting mirror (D) by double-colored beam splitter (C) and image position and forms, wherein double-colored beam splitter (C) is for being made by two prisms at 45 plated film gummed on the inclined-plane, the shortwave image can see through, and the long wave image is reflected.

6, diagnostic apparatus according to claim 1 is characterized in that image synthesizes and display system (15) is made up of image multichannel seizure recorder (25), spectrum picture processing synthesizer (26), four lattice image displays (27).

7, diagnostic apparatus according to claim 1 is characterized in that the control circuit of synchronous control system (16) is connected to form through circuit by the light source limit switch of the position-sensing switch of 2 picked-up different images, the transformation of 2 control lighting systems and the relay of control duty; Wherein, 2 light source limit switch L, K are arranged on the rotating disk of syncmotor, light hole (19), light filter (20) and shelf sheet (21) are arranged on the rotating disk of syncmotor, light source limit switch L, K are positioned at the both sides of shelf sheet (21), center of turntable had certain angle, light hole (19) and light filter (20) lay respectively at limit switch L, the centrosymmetry position of K, and rotating disk is installed on the syncmotor; Framing switch M, N are arranged at the edge of image channel selector dial (22), and dial (22) is provided with two picture access openings, and position-sensing switch M, N correspond respectively to the position of these two picture access openings, and there is corresponding angle at the dial center; Be installed in 4 relay J on the circuit board _M, J _N, J _L, J _KEach contact switch and corresponding framing switch M, N, light source limit switch L, K do corresponding the connection.

8, diagnostic apparatus according to claim 7 is characterized in that in the control circuit, and 220 volts of voltages become the 12V dc source behind transformator (P) and rectifier cell (U), and the 12V unidirectional current has four output loops: 1. pass through framing switch M to relay J _M2. coil power supply passes through framing switch N to relay J _N3. coil power supply passes through light source limit switch L to relay J _LCoil power supply, 4. pass through light source limit switch K to relay J _KCoil power supply; Position-sensing switch M is provided with two bypasses, and the one, by switch J _M1And J _N4Be composed in series, the 2nd, by switch J _M6With J _N6Be composed in series; Position-sensing switch N is provided with a bypass, by switch J _N1And J _M4Be composed in series; Limit switch L is provided with a bypass, by switch J _L1And J _K4Be composed in series; Limit switch K is provided with a bypass, by switch J _K1And J _L4Be composed in series; The syncmotor power supply circuits are that 220V inlet wire one end passes through capacitor C ₁Be connected on 3 feet of motor winding II, the 220V inlet wire other end directly is connected on 4 feet of motor winding II; And loop of 3 feet of motor winding II is by switch J _M2And J _L2Be connected with 2 feet of motor winding I, another loop is through switch J _M5And J _L5Link to each other with 1 foot of motor winding I; 4 feet of motor winding II also have two loops to link to each other with motor winding I: one is through capacitor C ₂, switch J _N5And J _K5Link to each other with 1 foot of motor winding I, another is by switch J _N2And J _K2Link to each other with 2 feet of motor winding I.

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