CN210005784U

CN210005784U - digital pathological imaging equipment

Info

Publication number: CN210005784U
Application number: CN201921009013.XU
Authority: CN
Inventors: 唐玉豪; 何俊峰; 吴庆军; 于綦悦; 韦建飞; 邓建; 刘亚鸿; 周雄兵; 王阳
Original assignee: Dakowei Shenzhen Medical Equipment Co Ltd
Current assignee: Dakowei Shenzhen Medical Equipment Co Ltd
Priority date: 2019-07-01
Filing date: 2019-07-01
Publication date: 2020-01-31
Anticipated expiration: 2029-07-01

Abstract

The utility model relates to the technical field of optical imaging, more specifically, it relates to digital pathology imaging devices, this digital pathology imaging device includes micro-lighting device, microobjective and digital image sensor, micro-lighting device includes light source, Mie scattering device, optical cavity and condensing lens, the light source is located the side of Mie scattering device, the condensing lens is located another side of Mie scattering device, the light source is used for sending out the light and shines on Mie scattering device, Mie scattering device is used for the light dispersion who shines into the light source and shines on the condensing lens, the condensing lens is used for focusing the light that the Mie scattering device shines into and exports on the testee, microobjective includes lens and the second lens that set gradually along the optical axis direction, the lens is used for receiving the light that shines into from the testee, lens front surface and second lens rear surface all are plated with half-transmitting and half-reflecting optical medium light splitting film, digital image sensor is used for receiving the light that shines into from the second lens, digital imaging is carried out.

Description

digital pathological imaging equipment

Technical Field

The utility model relates to an optical imaging technical field, in particular to kinds of digital pathology imaging device.

Background

The digital pathology refers to the application of computers and networks in the field of pathology, and is a technology of organically combining modern digital systems and traditional optical amplification devices.

The existing digital pathological imaging equipment generally comprises a microscope objective and a light source system, wherein light emitted by a light source is generally in Gaussian distribution, the brightness of the central area of a microscopic field of view is highest, the brightness of the periphery of the microscopic field of view is lower, and the problem of uneven illumination is solved.

In addition, the conventional microscope generally comprises an entrance pupil lens, an aperture stop, an intermediate lens or a combination of intermediate lenses, and an exit pupil lens, which is used to enlarge a local region of the observed object to realize the observation of the microscopic world, and the light from the observed object first passes through the entrance pupil lens and irradiates into the lens barrel, then is enlarged by the aperture stop and the intermediate lens, and finally irradiates out of the lens barrel through the exit pupil lens to realize clear imaging.

The performance of a microscope objective is mainly composed of: numerical aperture, field of view, magnification, effective focal length. The numerical aperture describes the size of the light-receiving cone angle of the objective, and directly determines the light-receiving capacity and optical resolution of the microscope objective, for example: the larger the numerical aperture is, the stronger the light receiving capacity of the microscope objective is, and the higher the optical resolution is; the field range is the range of an observed object which can be magnified and imaged by the microscope objective, the magnification is the proportion of the field range to the imaging area, and generally, under the condition that the imaging area is fixed, the larger the magnification is, the smaller the field range is, the more the number of the required intermediate lenses is (generally, the larger the number of the intermediate lenses is) so as to inhibit the aberration of high-magnification imaging; the effective focal length is the distance from the principal point of the optical system to the focal point on the optical axis, and the smaller the effective focal length is, the larger the magnification is, the smaller the visual field range is, and the larger the numerical aperture is.

However, according to the relationship among the parameters determining the performance of the microscope objective, the numerical aperture and the magnification factor are inevitably increased for clear imaging of the ultrastructure, which inevitably leads to reduction of the visual field range, increase of the number of the intermediate lenses, and abrupt increase of the volume, the manufacturing and production cost and the assembly difficulty of the microscope objective.

For example, in the field of pathological diagnosis, doctors must undertake microscopic observation tasks of more than 100 pathological sections every day, the conventional microscope is used, and due to the limitation of numerical aperture and magnification, doctors need to repeatedly switch microscope objectives with different magnifications when observing every sections so as to realize accurate observation of pathological sections from macroscopic structure to superfine structure and ensure the accuracy of pathological diagnosis, and due to the limitation of visual field range, doctors must operate a translation stage when carrying out microscopic observation so as to realize observation and diagnosis of local tissues in the whole section and prevent misdiagnosis and missed diagnosis, which indicates that the limitation of the performance of the conventional microscope increases the complexity of the optical microscope, the doctors usually need more than 20 minutes for observing pathological sections, the efficiency is extremely low, the labor and the intensity of the pathological doctors are huge, the physical and psychological burden of the pathological doctors are threatened, the missed diagnosis and the risk of pathological diagnosis increase , the labor and the cost of the optical microscope is also high, and the hospital is not beneficial to the large medical diagnosis cost.

Due to the defects of the light source system and the microscope objective, although the burden and labor intensity of a pathologist can be reduced to a certain extent at , and the pathological diagnosis accuracy is improved, the pathological diagnosis efficiency is still not improved, and is even lower than that of the traditional pathological diagnosis, so that the development of the digital pathological technology and the application of the digital pathological technology in clinic are severely limited.

SUMMERY OF THE UTILITY MODEL

In view of this, the utility model provides kinds of digital pathology imaging device, the main objective is to make the light that its light source sent more even to the numerical aperture of microscope objective, field of vision scope are all enough big while the volume is littleer, the cost is lower.

In order to achieve the above object, the utility model mainly provides the following technical scheme:

the embodiment of the utility model provides kinds of digital pathology imaging equipment, including micro-lighting device, micro-objective and digital image sensor;

the micro-lighting device comprises a light source, a Mie scattering device, an optical cavity and a condenser, wherein the light source is positioned on the side of the Mie scattering device, the condenser is positioned on the other side of the Mie scattering device, and the Mie scattering device is sleeved in the optical cavity;

the microscope objective comprises a th lens and a second lens which are sequentially arranged along the direction of an optical axis, and the microscope objective receives light emitted from a measured object through a th lens, wherein the surface of the th lens facing an object plane is a front surface, and the surface facing an image plane is a rear surface;

the digital image sensor is used for receiving the light entering from the second lens and carrying out digital imaging.

The utility model is further arranged in that the number of the micro-lighting devices is a plurality and the micro-lighting devices are arranged in sequence to form a micro-lighting device array;

the number of the micro objectives is equal to that of the micro lighting devices, and is , so as to form an objective lens array;

the number of digital image sensors is equal to the number of micro objectives and corresponds to to form a sensor array.

The utility model discloses step sets up to when the sensor array is used for moving along direction, the image that each digital image sensor becomes is arranged at no interval in proper order in the second direction, direction is perpendicular with the second direction.

The utility model discloses step is that the sensor array has N rows arranged in parallel at intervals along the direction, N is an integer more than or equal to 2;

the adjacent two rows are respectively an N1 th row and an N2 th row along the th direction, wherein N2 is N1+1, N1 is an integer greater than or equal to 1, the N2 th row is offset from the N1 th row along the second direction by a distance FoV, and the FoV is the size of an image formed by the digital image sensor in the second direction.

The utility model discloses step sets up to be that the sensor array has N rows that are arranged at parallel interval along the th direction, N is an integer more than or equal to 3, the number of the digital image sensors in two rows at the outermost side in the sensor array is equal and is M1, the number of the digital image sensors in other rows is M2, M1 is M2+ 1;

the adjacent two rows are respectively an N1 th row and an N2 th row along the th direction, wherein N2 is N1+1, N1 is an integer greater than or equal to 1, when N2 is smaller than N, the N2 th row is offset from the N1 th row along the second direction by a distance FoV, when N2 is equal to N, the N2 th row protrudes from the N1 th row along the second direction by a distance FoV, and the FoV is the size of an image formed by the digital image sensor in the second direction.

The utility model discloses a step is that the number of the digital image sensors in each row is more than two and the digital image sensors are arranged in sequence along the second direction;

two adjacent digital image sensors in each row are equidistant in the second direction and are r 1.

The utility model discloses a step is set as N is the minimum integer which is more than or equal to (W + r)/FoV;

r1＝N*FoV-W；

wherein W is the dimension of the digital sensor along the second direction, and r is the minimum interval that can be realized by the processing technology of two adjacent digital image sensors in the same rows in the second direction.

The utility model discloses step sets up to be that two adjacent lines are at the interval of side r2, and r2 is the minimum interval that digital image sensor's in two adjacent lines processing technology can realize in side.

The utility model discloses a step is that the digital pathology imaging device further comprises a fixing plate, and the fixing plate is provided with a mounting hole;

the number of the mounting holes is equal to that of the micro-objectives and corresponds to , each micro-objective is correspondingly mounted in the corresponding mounting hole, the th lens is positioned at the end of the mounting hole, and the second lens is positioned at the other end of the mounting hole.

The utility model discloses a step is that the outer diameter of the th lens is smaller than that of the second lens;

the mounting hole comprises an th hole section, a second hole section and a third hole section which are sequentially connected, and the outer diameters of the th hole section, the second hole section and the third hole section are sequentially reduced;

wherein the th lens is fixed on the th hole section, and the second lens is fixed on the third hole section.

The utility model discloses step sets up as be equipped with the th breach on the lateral wall of hole section, th breach intussuseption is filled with the light adhesive, th lens pass through the light adhesive fix on hole section;

and/or a second notch is formed in the side wall of the third hole section, optical adhesive is filled in the second notch, and the second lens is fixed on the third hole section through the optical adhesive.

The utility model discloses advance step and set up as be equipped with breach on the lateral wall of hole section and be equipped with the second breach on the lateral wall of third hole section, the breach is located hole section's end that is close to the second hole section, the second breach is located third hole section's end that deviates from the second hole section.

The utility model discloses step sets up to the second hole section is frustum shape, the central line of second hole section and lens or the coincidence of the central line of second lens.

The utility model discloses step sets up to, the light source is emitting diode, or semiconductor laser.

The utility model discloses step sets up to the mie scattering device is kinds of solid optical devices that distribute mie scattering medium particles, and this optical device is transparent, or translucent, and optical device's refracting index is less than mie scattering medium particle's refracting index.

The utility model discloses step is set up that the optics chamber is a hollow cylinder-shaped closed chamber which wraps the outside of Mie scattering device and has two open ends, and the inner wall is the mirror surface of the reflected light or the surface of the black oxidation layer.

The utility model discloses step sets up to be can contract even light propagation direction for the condensing lens, carry out the optical lens or the optical lens combination that spotlight shines.

The utility model discloses step sets up to the light source passes through optical cement to be fixed in the side of mie scattering device, and the condensing lens passes through optical cement to be fixed in another side of mie scattering device.

The utility model discloses step sets up to be that lens and second lens are circular lens, have the interval between lens and the second lens, are full of air or liquid in the interval, or are equipped with other lens and other lens combinations in the interval again.

The utility model discloses step sets up to, lens's the face type of front surface and back surface is the aspheric surface, and the front surface and the back surface of second lens are the aspheric surface.

The utility model discloses a step is that the digital pathological imaging device also comprises an image data acquisition controller, a data bus interface, a random access memory, a central processing unit, a nonvolatile memory and a display output port;

the digital image sensor is connected with the image data acquisition controller through a parallel data interface, and the image data acquisition controller is used for reading digital image data transmitted by the digital image sensor; the image data acquisition controller is connected with the random access memory through a data bus interface, and transmits digital image data to the random access memory through the data bus interface; the central processing unit is connected with the random access memory, the nonvolatile memory and the display output port through a circuit bus, and is used for reading the digital image data in the random access memory, storing the digital image data into the nonvolatile memory and outputting the digital image data to the display output port for displaying the image data.

The utility model discloses step sets up to image data acquisition controller and central processing unit for have serial calculation and logical processing's treater chip or electronic system, or have parallel calculation and logical processing's treater chip or electronic system, or have both serial and parallel calculation and logical processing's treater chip or electronic system.

The utility model discloses step sets up as, the data bus interface is the data bus and hardware interface from the image data acquisition controller to the random access memory.

The utility model discloses step sets up to, random access memory is the register that has data buffer access and/or, nonvolatile memory is the computer memory that the data that store can not disappear after the power is closed.

The utility model discloses step sets up as image data acquisition controller is used for the method or the communication protocol of parallel or serial receipt digital image sensor to handle image data acquisition, and adopts serial or parallel data processing algorithm, carries out the preliminary treatment to image data.

The utility model discloses step provides that the RAM is used for writing the bus interface data read in the mode of direct memory access.

The utility model discloses step sets up to central processing unit is used for reading the data of storage in the random access memory, writes the data of reading in the random access memory into the display output port with the mode of direct memory access.

The utility model discloses step sets up as, nonvolatile memory is used for reading the data of storage in the random access memory, writes into the random access memory data of reading with the mode of direct memory access.

Borrow by above-mentioned technical scheme, the utility model discloses digital pathology imaging device has following beneficial effect at least:

(1) the white light output by the micro-lighting device is uniform in illumination and spectral distribution, the illumination brightness of a traditional micro-light source is Gaussian distribution, the spectral distribution of different illuminations is not constant, the micro-lighting device can ensure higher light source utilization rate, the traditional light source is large in size and cannot ensure the light source utilization rate, the micro-lighting device is simple in structure and assembly, focusing illumination is achieved, only optical lenses are needed, the traditional light source can achieve illumination of a relatively uniform light source only by combining a plurality of lenses, the light source is provided with the light emitting diode, power consumption is low, price is low, and the light emitting diode can be continuously used for more than 5 ten thousand hours, so that the micro-lighting device is stable and reliable and long in service time compared with the traditional light source.

(2) The utility model discloses a micro objective adopts catadioptric structure, not only can realize the optical micro objective of high performance with few lens quantity, has increased the path length that light propagated in optical system moreover, makes micro objective reach its diffraction limit that can, and the optical performance with two lenses plays extremely delightly, the utility model discloses a micro objective is owing to reduced the quantity of lens when guaranteeing the high performance, brings the very big reduction of objective volume, the very big saving of manufacturing cost, and the very big reduction of production degree of difficulty, the utility model discloses a micro objective can realize assembling of formation of image light, forms high energy image focus, greatly promotes the SNR of formation of image, realizes the clear formation of image of high quality in big microscopic fields, the utility model discloses a micro objective satisfies optical microscope's miniaturization demand completely, especially, satisfies digital pathology high-speed scanning's demand completely, can promote traditional digital pathology scanning time more than 10 times, satisfies digital pathology technology's high efficiency and accurate application demand in clinical pathology diagnosis completely.

(3) The th lens array and the second lens array form a novel objective lens array, can simultaneously carry out microscopic imaging on a plurality of tissue areas with similar positions, and effectively realizes efficient pathological tissue chip observation and diagnosis and high-speed digital pathological scanning.

(4) The plurality of micro-lighting devices are sequentially arranged to form the micro-lighting device array, so that the lighting requirement of the micro-objective array can be met, and the illumination is more uniform.

(5) Through set up a plurality of mounting holes on the fixed plate, this a plurality of mounting holes are the array the same with micro objective arranges, and each micro objective can install in corresponding mounting hole correspondingly to can fix the micro objective who is the array and arranges.

(6) In the prior art, a central processing unit firstly receives image data transmitted by an interface of external equipment such as a USB and the like, secondly writes the data into a random access memory, secondly reads the data in the random access memory and sends the data into a display output port, after the display is finished, the data stays in a display cache, and then the central processing unit transmits the data in the random access memory to a nonvolatile memory through a bus. The process is controlled by the central processing unit, which generally causes slow data transmission, generally takes more than 10 seconds, even minutes, for example, when an interrupt processing task occurs, the central processing unit needs to suspend the current data transmission task, after the interrupt processing task is finished, the central processing unit needs to reply the data transmission task, and excessive interrupt processing tasks may cause the data transmission speed to be reduced.

The utility model discloses a method, data transmission process do not have central processing unit's intervention, and control program control central processing unit switches the data bus control right to bus controller to realize that data is direct from the bus to random access memory's transmission, under this condition, data transmission belongs to end-to-end transmission, does not have the interrupt, and bus transmission speed is big, can realize fast-speed data transmission more.

Additionally, the utility model discloses a method for the data transmission of demonstration belongs to concurrent data transmission with towards nonvolatile memory's data transmission, and the two goes on simultaneously, and belongs to direct memory reading and data transmission, therefore the upper limit of data speed is restricted at display port and nonvolatile memory speed, full play data bus transmission advantage, makes data transmission speed reach the limit.

The above description is only an overview of the technical solution of the present invention, and in order to make the technical means of the present invention clearer and can be implemented according to the content of the description, the following detailed description is made with reference to the preferred embodiments of the present invention and accompanying drawings.

Drawings

Fig. 1 is a simplified structural diagram of a digital pathology imaging apparatus provided by an embodiment of the present invention;

fig. 2 is a schematic structural diagram of kinds of micro-lighting devices provided by the present invention;

FIG. 3 is a schematic optical path diagram of the micro-illuminator of FIG. 2;

fig. 4 is a schematic view of the application of the microscope illumination device of the present invention in digital pathological microscopic imaging;

fig. 5 is a microscopic image when the microscopic lighting device of the present invention is used for lighting;

FIG. 6 is a microscopic image when illuminated using a conventional microscopic illumination apparatus;

fig. 7 is a structure and light path diagram of the microscope objective of the present invention;

FIG. 8 is a drawing showing the structure of th lens of the microscope objective of the present invention;

fig. 9 is a structural view of a second lens of the microscope objective of the present invention;

fig. 10 is a modulation transfer function MTF diagram of the microscope objective optical system according to the present invention;

fig. 11 is a light characteristic fan diagram of a longitudinal section of the microscope objective optical system according to the present invention;

fig. 12 is a light characteristic fan diagram of a cross section of a microobjective optical system according to the present invention;

fig. 13 is a longitudinal section optical path fan diagram of the microscope objective optical system of the present invention;

fig. 14 is a cross-sectional optical path fan diagram of the microscope objective optical system according to the present invention;

fig. 15 is a point diagram of the microscope objective optical system according to the present invention;

fig. 16 is a view field curvature diagram of the microscope objective optical system according to the present invention;

fig. 17 is a distortion diagram of the microscope objective optical system according to the present invention;

fig. 18 is a schematic structural view of an array of types of micro-lighting devices provided by the present invention;

fig. 19 is a cross-sectional view of a microscope objective array according to the present invention;

fig. 20 is a schematic imaging diagram of a microscope objective array according to the present invention;

fig. 21 shows an array arrangement of both types of micro objectives and a digital image sensor provided by an embodiment of of the present invention;

fig. 22 shows an array arrangement of microscope objectives combined with a digital image sensor according to another embodiment of the present invention;

fig. 23 illustrates an array arrangement of digital image sensors provided by of the present invention;

fig. 24 shows an array arrangement of digital image sensors according to another embodiment of the present invention;

fig. 25 is a schematic structural diagram of kinds of fixing plates provided in the example of the present invention;

fig. 26 is a schematic cross-sectional view of a kinds of micro-objectives provided by of the present invention, mounted on a fixing plate;

fig. 27 is a hardware implementation structure and a data processing flow chart of the digital image big data high-speed transmission of the digital pathology imaging device of the present invention;

fig. 28 is a hardware implementation structure diagram of the digital image big data high-speed transmission of the digital pathology imaging device of the present invention.

The reference numeral 1 denotes a microobjective, 2 denotes a digital image sensor, 3 denotes a microillumination device, 101 denotes a light source, 102 denotes an optical cavity, 103 denotes a mie scattering device, 104 denotes mie scattering medium particles, 105 denotes a condenser, 106 denotes a connection plate, 201 denotes light emitted from the light source, 202 denotes light scattered by the mie scattering medium particles, 203 denotes light scattered by the mie scattering medium particles and reflected on the optical cavity wall, 204 denotes light emitted by the mie scattering device, 205 denotes light collected by the condenser, 206 denotes a light exposure surface formed by the collected light, 301 denotes a micro LED light chip, 302 denotes a UV curable optical adhesive, 303 denotes a mie scattering micro rod, 304 denotes a nano microsphere, 305 denotes a transparent polycarbonate, 306, a lens barrel, 307 denotes a plano-convex lens, 308 denotes emitted light, 309 denotes a glass slide, 310 denotes observed cells, 311 denotes a cover glass, 402 denotes a conventional illumination center denotes light, 403 denotes a dark image, 50 denotes an object surface, denotes a semi-reflective optical medium, 505 denotes a second semi-transparent optical film, a transparent adhesive, a transparent film, a transparent cover glass, a transparent film, a transparent cover glass, a transparent.

Detailed Description

It should be noted that, if directional indicators (such as upper, lower, left, right, front, and back … …) are involved in the embodiments of the present invention, the directional indicators are only used to explain the relative position, motion, etc. of the components in a specific pose (as shown in the drawings), and if the specific pose changes, the directional indicators will change accordingly.

As shown in fig. 1, the embodiments of the present invention provide digital pathological imaging apparatuses, including a microscope objective 1, a digital image sensor 2 and a microscope illumination device 3. as shown in fig. 2, the microscope illumination device 3 includes a light source 101, a mie scattering device 103, an optical cavity 102 and a condenser lens 105, the light source 101 is located on side of the mie scattering device 103, the condenser lens 105 is located on another side of the mie scattering device 103, the mie scattering device 103 is sleeved in the optical cavity 102, the light source 101 is used for emitting light to the mie scattering device 103, the mie scattering device 103 is used for scattering the light incident from the light source 101 to irradiate the condenser lens 105, the condenser lens 105 is used for outputting the light incident from the mie scattering device 103 to a measured object such as a cell 301 to be observed, as shown in fig. 7, the microscope objective 1 includes a th lens 502 and a second lens 505 sequentially arranged along an optical axis direction, the microscope objective 1 receives the light incident from the measured object through a th lens 502, the front surface of the second lens 502 is a front object surface 505, the second lens 505 is a semi-transparent film coated with a semi-transparent film 507, and a semi-transparent film for receiving optical image receiving film for receiving optical film for receiving light from the image receiving surface of the image receiving film 502, and outputting light receiving film 507, the image receiving film, wherein the image receiving film, the second lens 502 is coated with a semi-optical film 507, the semi-transparent film receiving film for receiving film, the semi.

The technical principle of the micro-lighting device 3 is that as shown in fig. 2 and fig. 3, solid optical devices filled with mie scattering medium particles 104 are core devices of the micro-lighting device 3, the solid optical devices are transparent or semitransparent solids, the materials of the solid optical devices are optical resin or optical glass, and the solid optical devices have the performance of uniformly scattering and outputting incident light beams, a light source 101 and a condenser lens 105 are respectively arranged on two sides of the mie scattering device 103, the light source 101 can be fixed on a side of the mie scattering device 103 through optical glue, the condenser lens 105 can be fixed on the other side of the mie scattering device 103 through optical glue, the light source 101 end is a light beam incident end, the condenser lens 105 end is a light beam output end, in order that the incident light enters the mie scattering device 103 and is not transmitted from the device, a hollow lens barrel 306 (as shown in fig. 4) is wrapped on the outer side of the mie scattering device 103, in order to improve the light utilization rate of the light source 101, the inner wall of the lens barrel 306 can be subjected to total reflection film coating treatment, in order to.

After the light beam emitted by the light source 101 irradiates the mie scattering device 103, because the inside of the device is filled with medium particles, a large amount of mie scattering occurs when the light beam encounters the particles, and the scattered light is continuously scattered and superposed in the process of passing through the mie scattering device 103, and finally, light with uniform illumination is output.

When the inner wall of the lens barrel 306 is a total reflection coating, the light scattered in the mie scattering device 103 is reflected by the inner wall of the lens barrel 306 and is scattered, superimposed and reflected continuously in the period, so that the light intensity loss is less, and the light intensity output by the mie scattering device 103 is brighter.

When the inner wall of the lens barrel 306 is subjected to black oxidation treatment, the light scattered in the mie scattering period irradiates the inner wall of the lens barrel 306, and is not reflected or the reflected light is extremely weak, so that the loss of light transmitted in the mie scattering device 103 is large, and the light intensity output in the mie scattering period is weak.

However, based on the mie scattering theory, the degree of mie scattering is independent of the wavelength, and the property after photon scattering remains the same, so that a stable uniform white output is obtained through the mie scattering device 103 even though the three light emitting diodes are located at different positions, and focal points can be formed through the condenser lens 105.

When the light source 101 is a white light emitting diode, the spectral components of the white light emitted by every diodes are different, but based on the above mie scattering theory, the white light output by the mie scattering device 103 can form a stable and uniform white light output despite the different light emitting diodes, thereby improving the stability of the light source 101.

Fig. 3 is a schematic light path diagram of the uniform light micro-lighting device 3 based on mie scattering of the present invention. The arrow 201 indicates light emitted from the light source 101, the arrow 202 indicates light scattered by the mie scattering medium particles 104, the arrow 203 indicates light scattered to be irradiated on the wall of the optical cavity 102 and reflected, the arrow 204 indicates light emitted by the mie scattering device 103, the arrow 205 indicates light condensed by the condenser lens 105, and the arrow 206 indicates a light irradiation surface formed by condensing light.

The light source 101 may be a light emitting diode or a semiconductor laser, the mie scattering device 103 may be solid optical devices in which the mie scattering medium particles 104 are distributed, the mie scattering medium particles 104 are distributed inside the solid optical devices, the optical devices are transparent or semi-transparent, the refractive index of the optical devices is smaller than that of the mie scattering medium particles 104, the optical cavity 102 may be a hollow cylindrical closed cavity which is wrapped outside the mie scattering device 103 and is opened at two ends, the inner wall of the hollow cylindrical closed cavity is a mirror surface for reflecting light, or a black oxide layer surface, the condenser lens 105 is optical lenses or optical lens combinations which can shrink the uniform light propagation direction and condense and irradiate.

In specific application examples, as shown in fig. 4, the light source 101 may be a micro LED light emitting chip 301, the mie scattering device 103 may be a mie scattering micro rod 303, the optical cavity 102 may be a lens barrel 306, and the condenser lens 105 may be a plano-convex lens 307, in this example, the mie scattering-based uniform light micro-lighting device 3 includes the micro LED light emitting chip 301, the mie scattering micro rod 303, the lens barrel 306, and the plano-convex lens 307, the mie scattering micro rod 303 is a small cylindrical optical device of a 1-100 nm diameter nano microsphere 304 doped with lactic-glycolic acid (PLGA) or polyvinyl alcohol (PVA) as a material, the nano microsphere 304 is the aforementioned mie scattering medium particles 104, the diameter of the cylindrical body is the same as or similar to the diameter of the LED light emitting portion, the refractive index of the polycarbonate is smaller than the refractive index of the nano microsphere 304, the distribution of the nano microsphere 304 is random, so that incident light is irradiated to the nano microsphere 304, thereby causing mie scattering, the mie scattering medium particles 306 is the mie scattering, the diameter of the cylindrical scattering medium particles is the diameter of the surface of the LED light emitting portion is the same as or similar to the diameter of the light emitting surface of the light emitting rod 303, the light emitting surface of the light emitting rod is adhered to the light emitting surface of the light emitting rod 303, the light emitting surface of the light emitting rod 301, the light emitting surface of the light emitting rod 303, the light emitting surface of the light emitting rod is adhered to have a focal point of the surface of the light emitting surface of the.

The embodiments of the homogeneous light microscope illumination device 3 based on mie scattering are used in such a way that, as shown in fig. 4, the micro LED light emitting chip 301 is first energized, the LED surface emits light, the light beam is mie scattered inside the mie scattering micro rod 303, so that homogeneous white light is output from the mie scattering micro rod 303 and irradiated on the plane surface of the plano-convex lens 307, and the homogeneous white light, i.e., the outgoing light 308 of the plano-convex lens, is converged and irradiated on the focal point of the plano-convex lens 307 by the refraction of the plano-convex lens 307, at this time, if the observed object is the observed cell 310 on the tissue slice, the tissue slice is located between the slide 309 and the cover glass 311, the tissue slice is located at the homogeneous white light converging focal point, the homogeneous white light is transmitted through the tissue slice forming object light and irradiated into the microscope objective 1 of the optical microscope, the object light is amplified and imaged on the digital image sensor 2 by the microscope optical system, a digital microscope image is formed by reading and encoding the data of the digital image of the digital slide 2 by a computer, and the background light irradiated on the tissue cell is different from the homogeneous white light, so that the background light is not uniformly distributed on the original digital image.

Wherein, figure 5 is the use the utility model discloses kinds of microscopic image when the even light micro-lighting device 3 based on mie scattering throws light on, figure 6 is the microscopic image when using the illumination of traditional micro-lighting device, 402 among figure 6 is bright in the middle of the image when using traditional illumination, 403 is dark all around for using the image when traditional illumination, through contrast 5 and figure 6, can see that the utility model discloses the white light of well micro-lighting device 3 output, the illumination is even, and spectral distribution is even, and traditional micro light source illumination is bright and is gaussian distribution, and the illumination is inhomogeneous.

First, as shown in FIG. 7, a th lens 502 and a second lens 505 are sequentially included from the surface of an object to be observed (object plane 50) to the image formation surface (image plane 507) along the optical axis direction, the th lens 502 is a meniscus lens, the front surface facing the object plane 50 is a concave surface, the rear surface facing the image plane 507 is a convex surface, the second lens 505 is a meniscus lens, the front surface facing the object plane 50 is a concave surface, the rear surface facing the image plane 507 is a convex surface, the curvatures of the front and rear surfaces of the th lens 502 and the second lens 505 are different, and an aperture stop is located at the position of the rear surface of the th lens 502.

As shown in fig. 7 to 9, the front surface of the th lens 502 and the rear surface of the second lens 505 are both coated with the transflective optical medium light splitting film, wherein the transflective optical medium light splitting film is kinds of optical coatings, and is capable of transmitting and continuously propagating incident light along an incident direction, reflecting and continuously propagating incident light along an opposite incident direction, the light transmitted and continuously propagating along the incident direction is transmitted light, the light emitted along the opposite incident direction and continuously propagating along the opposite incident direction is reflected light, and according to the energy conservation law, the sum of the energies of the reflected light and the transmitted light is equal to the energy of the incident light, specifically, the sum of the intensities of the reflected light and the transmitted light is equal to the intensity of the incident light.

In specific application examples, the specific performance parameters of the microscope objective 1 may be that the diameter of the field range is 1 mm, the numerical aperture is 0.6, the effective focal length is 0.78 mm, the diameter of the entrance pupil is 1.17 mm, the field range is 1.17 mm, the total length of the system is 4.23 mm, the magnification is 5.14 times, the imaging resolution is 0.24 microns/pixel, the operating wavelength is in the visible light wavelength region of 0.4 microns to 0.7 microns, the design wavelengths are 0.643 microns, 0.591 microns, 0.542 microns, 0.5 microns and 0.466 microns, wherein the design center wavelength is 0.542 microns, and the above parameters meet the implementation requirements of optical microscope imaging and device miniaturization, and meet the implementation requirements of digital pathology scanning efficiency improvement and high-quality microscope imaging.

The main performance parameters of the microscope objective 1 can specifically satisfy the following relations:

numerical aperture versus working medium refractive index and half angle of maximum cone angle of incident light:

NA ═ n × sin θ - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - -formula 1

Where NA represents the numerical aperture, n represents the refractive index of the working medium, and θ represents the half angle of the maximum cone angle of incident light.

Relationship between half angle of maximum cone angle of incident light and entrance pupil diameter and effective focal length:

tan θ ═ EPD/(2 × EFL) - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - -

Where θ represents the half angle of the maximum cone angle of incident light, EPD represents the entrance pupil diameter, and EFL represents the effective focal length.

The relationship between imaging resolution and magnification and field of view:

δ＝ρ²- - (Mag. U) - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - - -

Where δ represents an imaging resolution, ρ represents a pixel size of the image sensor, Mag represents a magnification, and U represents a unit length; in this example ρ is specifically 1.12 microns, U is specifically 1 micron, and Mag is specifically 5.14, so the imaging resolution is specifically 0.24 microns per pixel.

In specific application examples, the th lens 502 and the second lens 505 may be NLAF35 (Vd ═ 2.6444) and NSK16(Vd ═ 0.0007) materials of SCHOTT corporation, or NBF2(Vd ═ 0.9575) materials of HOYA corporation, or NBF2(Vd ═ 0.9575) materials of SCHOTT corporation, mbn 15(Vd ═ 2.1589) materials of SCHOTT corporation, or hdaf 82 (Vd ═ 733) materials of SCHOTT corporation, or hdaf 0.2680 (Vd ═ z 2.0274) materials of SCHOTT corporation, or hdaf 0.2680 (vdzvd ═ 4642) materials of SCHOTT corporation.

The embodiments of the micro objective lens 1 are, as shown in fig. 7, specifically, an object plane 50, a lens 502, a second lens 505, and an image plane 507, which are respectively arranged from left to right along an optical axis direction, wherein the object plane 50 is located at the leftmost side and is finite, the image plane 507 is located at the rightmost side and is finite, and the front surface of the lens 502 and the rear surface of the second lens 505 are respectively plated with a semi-transparent and semi-reflective optical medium light splitting film, specifically, semi-transparent and semi-reflective optical medium light splitting films, which utilize optical properties thereof to realize transmission of light incident on the surface of the film, parts and parts.

In the embodiments of the microobjective 1, as shown in fig. 7, the light propagation path in the system is specifically as follows, firstly, along the optical axis direction, the light from the observed object irradiates to the front surface of the lens 502 plated with the semi-transparent semi-reflective optical medium spectroscopic film 501, the front surface of the lens 502 faces to the object plane 50 and is concave, the image plane 507 faces to the convex surface, the curvature of the semi-transparent semi-reflective optical medium spectroscopic film 501 is the same as that of the front surface of the lens 502, the light reflected by the front surface plating film of the lens 502 of the incident light is not imaged, the other part of the transmitted light passes through the lens 502 and the rear surface thereof and irradiates to the front surface of the second lens 505, the object plane 50 of the lens 502 faces to the concave surface, the image plane 507 faces to the convex surface, the front surface of the second lens 505 faces to the object plane 50 and is concave, the light facing to the convex surface 507 faces to the object plane, the light rays pass through the front surface of the second lens 505 and irradiate to the second semi-reflective optical medium spectroscopic film 505, the rear surface of the second lens 505 faces to the concave surface 507, the optical medium is concave surface of the second lens 505, the rear surface of the semi-reflective optical medium is concave surface 507 faces to the second lens 505, the optical medium reflective semi-reflective optical medium reflective film 507 is concave surface of the second lens 505, the second.

The light which enters the optical system again is focused by the second lens 505, enters the th lens 502 again, is reflected by the th half-transmitting and half-reflecting optical medium light splitting film 501 on the front surface of the th lens 502, and finally is focused and irradiated on the image surface 507, so that the th light scattered transmission light is transmitted on the image surface 507, and meanwhile, the reflected light is focused, but the illumination intensity of the focused light is far greater than that of the scattered light, so that a high-definition high-quality microscopic image with high signal-to-noise ratio can be formed on the image surface 507.

According to the imaging principle, light components on the image surface 507 are completely transmitted light which is scattered and does not form a focus, and multiple reflected light which is converged and forms an imaging focus, the multiple reflected light is irradiated to be far higher than times of completely transmitted light, the completely transmitted light is noise in imaging, and the multiple reflected light is imaging, so that the signal-to-noise ratio of imaging contrast noise is high, and even if the completely transmitted light exists, clear imaging is not greatly influenced.

The th lens 502 and the 505 th lens can be both round lenses, the th lens 502 and the 505 th lens have a space between them, the space can be filled with air or liquid, or other lenses and other lens combinations can be arranged in the space, the front surface and the back surface of the th lens 502 can be both aspheric, and the front surface and the back surface of the 505 th lens can be both aspheric.

The design data of the optical system of the microscope objective 1 disclosed by the utility model can be shown in table 1. table 1 shows the specific design parameter values of each lens surfaces and the semi-transparent semi-reflective optical medium light splitting film in the optical system of the microscope objective 1 in the embodiments.

Table 1 shows the design parameters of the microscope objective optical system of the present invention.

Fig. 10 shows the modulation transfer function MTF of the microscope objective optical system of the present embodiment, approaching the diffraction limit. Fig. 11 shows the light ray characteristics of the longitudinal section of the optical system of the present embodiment, and fig. 12 shows the light ray characteristics of the cross section of the optical system of the present embodiment. Fig. 13 shows an optical path length characteristic diagram of a longitudinal section of the optical system of this embodiment, and fig. 14 shows an optical path length characteristic diagram of a cross section of the optical system of this embodiment. Fig. 15 shows a dot diagram of the optical system of the present embodiment. Fig. 16 shows a field curvature diagram of the optical system of the present embodiment, and fig. 17 shows a distortion diagram of the optical system of the present embodiment. The performance graphs show that the optical system of the microscope objective has good optical performance, the imaging quality is close to perfect imaging, and the requirements of optical microscopic observation and digital pathological imaging are completely met.

, as shown in FIG. 18, the number of the micro-lighting devices 3 can be multiple and arranged in sequence to form a micro-lighting device array, as shown in FIG. 19, the number of the micro-objective lenses 1 is equal to the number of the micro-lighting devices 3 and corresponds to form an objective lens array, in the objective lens array, each th lens 502 is arranged in sequence to form a th lens array, and each second lens 505 is arranged in sequence to form a second lens array, as shown in FIG. 21 and FIG. 22, the number of the digital image sensors 2 is equal to the number of the micro-objective lenses 1 and corresponds to form a sensor array.

The th lens array and the second lens array form a novel objective lens array, can perform simultaneous microscopic imaging on a plurality of tissue areas with similar positions, effectively realizes efficient pathological tissue chip observation and diagnosis and high-speed digital pathological scanning, and is sequentially arranged by a plurality of microscopic lighting devices 3 to form a microscopic lighting device array, so that the lighting requirement of the microscopic objective lens 1 array can be met, and the illumination is more uniform.

As shown in fig. 18, the present invention may further include a connection board 106, wherein the optical cavities 102 of the micro-lighting devices 3 may be sequentially arranged on the connection board 106, specifically, a plurality of through holes penetrating through both ends may be sequentially disposed on the connection board 106 at intervals, wherein each through hole is optical cavities 102, each mie scattering device 103 is correspondingly sleeved in the corresponding optical cavity 102, in this example, each mie scattering device 103 is conveniently fixed by the connection board 106, so that each mie scattering device 103 forms whole bodies.

Further , as shown in FIG. 21 and FIG. 22, the digital image sensors 2 are arranged in sequence without space in the second direction when the sensor array is used to move along the direction, and the direction is perpendicular to the second direction, wherein the direction may be the X direction in FIG. 1 and FIG. 2, and the second direction may be the Y direction in FIG. 1 and FIG. 2.

Specifically, because each digital image sensor 2 is arranged in an array, each of the microscope objectives 1 corresponding to the digital image sensor 2 is also arranged in an array, and because each of the microscope objectives 1 is held stationary relative to the digital image sensor 2 , the objective array formed by the microscope objectives 1 moves synchronously with the sensor array, and when the sensor array and the microscope objective 1 array move in the direction, such as in the X direction in fig. 1 and 2, each of the microscope objectives 1 in the microscope objective 1 array simultaneously scans portions of the tissue slice, such that the images formed by each of the digital image sensors 2 are arranged in a second direction, such as the Y direction, without gaps therebetween.

In the technical scheme, when the microscope objective 1 array and the digital image sensor 2 array perform linear scanning on tissue slices in a single direction, microscope images can be shot and spliced in parallel, the speed is improved by more than 20 times compared with that of a conventional method in the prior art, the user experience of a digital pathology scanner is greatly improved, and the application value of digital pathology is really realized.

Since each of the micro-objectives 1 corresponds to the digital image sensor 2 , the arrangement and method of the sensor array and the array formed by each of the micro-objectives 1 are .

The digital image sensors 2 in the sensor array may have various arrangements, such as an oblique -shaped arrangement or a zigzag arrangement.

In an example where the digital image sensors 2 in the sensor array are arranged in an oblique pattern, as shown in fig. 21, the sensor array may have N parallel rows spaced apart from each other along the direction, where N is an integer greater than or equal to 2, two adjacent rows are respectively the N1 th row and the N2 th row along the direction, N2 is N1+1, N1 is an integer greater than or equal to 1, the N2 th row is offset from the N1 th row along the second direction by a distance of FoV, and FoV is a dimension of the image formed by the digital image sensors 2 in the second direction.

In the above example, N ═ 6 is specifically exemplified. As shown in fig. 21, the sensor array has the 1 st, 2 nd, 3 rd, 4 th, 5 th and 6 th rows in the X direction in this order. Where row 2 is offset in the Y direction by the distance of FoV from row 1. Line 3 is offset in the Y direction by the distance of FoV from line 2. Row 4 is offset in the Y direction by the distance of FoV from row 3. Line 5 is offset in the Y direction by the distance of FoV from line 4. Line 6 is offset in the Y direction by the distance of FoV from line 5.

In an example in which the digital image sensors 2 in the sensor array are arranged in a zigzag manner, as shown in fig. 22, the sensor array has N rows arranged at intervals in parallel in the th direction, N is an integer greater than or equal to 3, the number of the digital image sensors 2 positioned in the outermost two rows in the sensor array is equal to and M1, the number of the digital image sensors 2 in the other rows is M2, M1 is M2+1, the adjacent two rows are respectively the N1 th row and the N2 th row in the th direction, N2 is N1+1, N1 is an integer greater than or equal to 1, when N2 is less than N, the N2 th row is offset from the N1 th row in the second direction by a distance of FoV, and when N2 is equal to N, the N2 th row protrudes from the N1 th row in the second direction by a distance of FoV, and FoV is a size of the image of the digital image sensors 2 in the second direction.

In the above example, N is 6, specifically exemplified, as shown in fig. 22, the sensor array has the 1 st row, the 2 nd row, the 3 rd row, the 4 th row, the 5 th row and the 6 th row in the X direction in this order, the number of the digital image sensors 2 in both the 1 st row and the 6 th row is equal, and the number of the digital image sensors 2 in the 2 nd row to the 5 th row is equal, the number of the digital image sensors 2 in the 1 st row is more than the number of the digital image sensors 2 in the 2 nd row, wherein the 2 nd row is shifted by the distance of FoV in the Y direction from the 1 st row, the 3 rd row is shifted by the distance of FoV in the Y direction from the 2 nd row, the 4 th row is shifted by the distance of FoV in the Y direction from the 3 rd row, the 5 th row is shifted by the distance of FoV in the Y direction from the 5 th row.

At step , as shown in fig. 21 and 22, the number of the digital image sensors 2 in each row may be two or more, and the two digital image sensors 2 in each row are sequentially arranged along the second direction, and the distances between two adjacent digital image sensors 2 in each row in the second direction are equal and are r 1.

In specific application examples, the corresponding arrangement parameters of the sensor array can be obtained by the following formula, where N is the minimum integer greater than or equal to (W + r)/FoV, r1 is N FoV-W, W is the dimension of the digital image sensor 2 along the second direction, and r is the minimum distance that can be achieved by the processing process of two adjacent digital image sensors 2 in the same line in the second direction.

The distance between the adjacent two rows in the -th direction is r2, and r2 is the minimum distance that can be achieved by the manufacturing process of the digital image sensors 2 in the adjacent two rows in the -th direction.

The arrangement parameters calculated by the formula can enable the sensor array to have a minimum arrangement structure, when tissue slices in the same size area are scanned, the size of the sensor array arranged by the method is small, and the effective utilization rate of each digital image sensor 2 in the sensor array is high.

Here, it should be noted that: the aforementioned FoV can be obtained by image measurement of the digital image sensor 2. W may be obtained by measuring the size of the digital image sensor 2. r can be obtained by process evaluation.

The following is a specific example of a sensor array in a zigzag arrangement.

In the th embodiment, as shown in FIG. 23, arrays of digital image sensors 2, the digital image sensors 2 have a width W of 5.18 mm, a height H of 5.4 mm, an imaging range FoV of 1.0 mm, and the digital image sensors 2 are bonded and packaged together with a minimum lateral spacing r of 0.8 mm and a minimum longitudinal spacing r2 of 0.82 mm.

Thus, the number of rows N of the array is calculated as follows:

(1)(W+r)/FoV＝(5.18+0.8)/1＝5.98。

(2) the number of rows N of the array is the smallest integer greater than or equal to 5.98, i.e., the number of rows N of the array is 6.

(3) The interval r 1N FoV-W6 1-5.18 0.82 between two adjacent digital image sensors 2 in the same line .

The specific number of the digital image sensors 2 in each row may be determined according to actual situations, and is not described herein again.

In a second embodiment, illustrated in FIG. 24, an array of digital image sensors 2, the digital image sensors 2 having a width W of 8.5 mm, a height H of 8.5 mm, an imaging range FoV of 1.0 mm, the digital image sensors 2 being bonded and packaged as specified by the packaging process, a minimum lateral spacing r of 0.3 mm and a minimum longitudinal spacing r2 of 0.3 mm.

Thus, the number of rows N of the array is calculated as follows:

(1)(W+r)/FoV＝(8.5+0.3)/1＝8.8

(2) the number of rows N of the array is the smallest integer greater than or equal to 8.8, i.e., the number of rows N of the array is 9.

(3) The interval r 1N FoV-W9 1-8.5 0.5 between two adjacent digital image sensors 2 in the same line .

, as shown in fig. 25 and 26, the digital pathology imaging apparatus of the present invention further includes a fixing plate 61, the fixing plate 61 is provided with mounting holes 62, the number of the mounting holes 62 is equal to the number of the microscope objectives 1, and corresponds to the number of the

microscope objectives

1, 1 corresponds to the mounting holes 62, the th lens 502 is located at the end of the mounting hole 62, and the second lens 505 is located at the end of the mounting hole 62.

Specifically, the plurality of mounting holes 62 on the fixing plate 61 are arranged in the same array as the microscope objectives 1, and after each microscope objective 1 is correspondingly mounted in the corresponding mounting hole 62, the microscope objectives 1 arranged in the array can be fixed.

In the technical scheme provided above, a plurality of conventional brackets are integrated at to form a -type fixing bracket (i.e. fixing plate 61) with array mounting holes 62, so that the wall thickness of the conventional bracket is reduced, and the integrated fixing of the array type micro objective 1 is realized.

In specific application examples, as shown in FIG. 26, the outer diameter of the aforementioned lens 502 is smaller than that of the second lens 505. the mounting hole 62 comprises a hole section 601, a second hole section 602 and a third hole section 603 which are connected in sequence, the outer diameters of the hole section 601, the second hole section 602 and the third hole section 603 are reduced in sequence, wherein the lens 502 is fixed on the hole section 601, and the second lens 505 is fixed on the third hole section 603. in this example, the hole section 601 and the third hole section 603 are both short in length and mainly used for fixedly mounting the lens 502 and the second lens 505. light exiting from the lens 502 can be irradiated onto the second lens 505 through the second hole section 602.

In the above example, by processing the hole section corresponding to the outer diameter of the lens, the lens fixing device has the effect of facilitating the installation of the lens, saves the volume of the fixing bracket, and is beneficial to the miniaturization of the fixing bracket.

, as shown in fig. 25 and 26, the hole segment 601 may have a 0 th notch 621 on the sidewall thereof, the notch 621 is filled with a photo adhesive 64, the th lens 502 is fixed on the hole segment 601 by the photo adhesive 64, wherein, in order to ensure the fixing effect of the th lens 502, preferably, the notch 621 may be two or more and evenly distributed in a circle around the hole segment 601, and in specific application examples, the th notch 621 is four.

Similarly, as shown in fig. 25 and 26, the sidewall of the third hole segment 603 may be provided with a second notch 622, and the second notch 622 is filled with the optical adhesive 64, the second lens 505 is fixed on the third hole segment 603 by the optical adhesive 64, wherein, in order to ensure the fixing effect of the second lens 505, preferably, the number of the second notches 622 may be more than two, and the second notches 622 are uniformly distributed in a circle around the third hole segment 603, and in specific application examples, the number of the second notches 622 is four.

Step , as shown in fig. 26, when the th notch 621 is disposed on the sidewall of the th hole segment 601 and the second notch 622 is disposed on the sidewall of the second hole segment 602, the th notch 621 mentioned above may be located at the end of the th hole segment 601 close to the second hole segment 602, and the second notch 622 is located at the end of the third hole segment 603 away from the second hole segment 602.

, as shown in FIG. 26, the second hole section 602 can be in a frustum shape, and the center line of the second hole section 602 coincides with the center line of the lens 502 or the second lens 505. because the light emitted from the lens 502 is divergently irradiated onto the second lens 505 in a cone shape, the second hole section 602 is shaped to match the shape of the light beam of the lens 502, which has the effect of saving the space of the fixing bracket, so that the outer diameter of the second hole section 602 is not too large and the structural strength of the fixing bracket is not affected.

Further , as shown in fig. 27, the digital pathology imaging apparatus of the present invention may further include an image data acquisition controller 7, a data bus interface 8, a random access memory 9, a central processing unit 10, a non-volatile memory 11, and a display output port 12.

The digital image sensor 2 is connected with an image data acquisition controller 7 through a parallel data interface, and the image data acquisition controller 7 is used for reading digital image data transmitted by the digital image sensor 2; the image data acquisition controller 7 is connected with the random access memory 9 through a data bus interface 8, and the image data acquisition controller 7 transmits digital image data to the random access memory 9 through the data bus interface 8; the central processing unit 10 is connected to the random access memory 9, the nonvolatile memory 11 and the display output port 12 through a circuit bus, and the central processing unit 10 is configured to read the digital image data in the random access memory 9, store the digital image data in the nonvolatile memory 11, and output the digital image data to the display output port 12 for displaying the image data.

The aforementioned digital image sensor 2 may be a sensor having photoelectric conversion and generating a digital signal, both the image data acquisition controller 7 and the central processor 10 may be a processor chip or an electronic system having serial calculation and logic processing, or a processor chip or an electronic system having parallel calculation and logic processing, preferably, the image data acquisition controller 7 and the central processor 10 may be a field programmable array, or a central processing unit, the aforementioned image data acquisition controller 7 is used for receiving a method or a communication protocol of the image acquisition device in parallel or in series to perform image data acquisition processing, the image data acquisition controller 7 also performs preprocessing on the image data using a method of serial or parallel data calculation, which may be a conversion calculation method of an image data format, and/or a calculation method of image data compression, and/or a calculation method of image color adjustment, the central processor 10 is used for reading data stored in the random memory 9, and writing the data read in the random memory 9 into the display output port 12 in a direct memory access manner.

The aforementioned data bus interface 8 may be a data bus and hardware interface from the image data acquisition controller 7 to the random access memory 9. Preferably, the data bus interface 8 is a PCI-express bus and interface, or a USB bus and interface, or a parallel transmission bus and interface. The aforementioned random access memory 9 may be a register having data buffer access. Preferably, the RAM 9 is a pre-memory buffer, or a double data rate RAM or a double data rate SDRAM. The random access memory 9 is used to write the read bus interface data in a direct memory access manner.

The aforementioned nonvolatile memory 11 may be a computer memory in which stored data does not disappear after the power is turned off. Preferably, the nonvolatile memory 11 is a read-only memory, or a magnetic disk memory, or a solid hard disk memory. The nonvolatile memory 11 is used for reading data stored in the random access memory 9 and writing the read data in the random access memory 9 in a direct memory access manner.

The utility model discloses a kind are towards large-scale image data collection of computer, transmission, demonstration, storage method, specifically are the digital image big data that come with the transmission of digital image collection equipment such as many digital cameras or digital scanner upload digital image processing system and show in real time and high-speed storage's method at a high speed to solve traditional data transmission method and can't realize the high-speed transmission of short time, show slow problem to digital image big data.

high-speed transmission method of large digital image data, is new data high-speed transmission technique for high-speed transmission, display and storage of large digital image data, firstly, the image data acquisition controller 7 reads data from the digital image sensor 2, the image data is preprocessed by color adjustment, data format conversion and data compression through the data processing unit integrated in the image data acquisition controller 7, then the large digital image data is sent to the data transmission bus, then the control program running on the central processor 10 switches the control right of the central processor 10 and the bus controller to the data transmission bus, the large data read to the data transmission bus is written into the random access memory 9 through the direct memory access mode, finally the control program returns the control right of the data transmission bus to the central processor 10 through the bus controller, the data in the random access memory 9 is directly written into the data display port through the data transmission bus and the direct memory access mode, and the background large image data is automatically written into the non-volatile memory 11 through the direct memory access mode while the image data is displayed, thus realizing the high-speed image data and non-volatile image data storage.

The utility model discloses in, when data spread into RAM 9, do not pass through central processing unit 10, but in the RAM 9 of directly writing in through data bus, consequently data transmission speed on the data bus and RAM 9's data transmission speed's minimum has decided the utility model discloses data transmission speed's maximum value, when data bus adopted PCI express 3.016 channel interface, highest transmission speed was 252Gbit/s, when RAM 9 adopted DDR4 PC4-34100, highest transmission speed was 272.8Gbit/s, consequently, under this kind of condition, the utility model discloses a highest transmission speed is 252Gbit/s, to the transmission of the digital pathology full section image of data volume about 32Gbit, the shortest transmission time is about 0.13 seconds, accords with real-time data transmission's needs.

The utility model discloses in, when data spread into display output port 12, central processing unit 10 directly reads the data in the random access memory 9, send it into display output port 12, consequently random access memory 9's data transmission speed and display output port 12 data transmission speed's minimum has decided the utility model discloses display output speed's maximum value, when random access memory 9 adopted DDR4 SDRAM PC4-34100, the highest transmission speed was 272.8Gbit/s, when display output port 12 adopted HDMI2.1 interface protocol, the highest transmission speed was 48Gbit/s, consequently, under this kind of condition, the utility model discloses a highest display output speed is 48Gbit/s, to the transmission of the digital pathology full section image of data volume about 32Gbit, the shortest transmission time is about 0.7 seconds, accords with high-speed data display's needs.

The utility model discloses in, when central processing unit 10 directly read the data in the random access memory 9 and sent into display output port 12, also sent data into nonvolatile memory 11 through data bus, consequently random access memory 9 'S data transmission speed and nonvolatile memory 11' S data transmission speed 'S minimum has decided the utility model discloses the maximum value of data storage speed, when random access memory 9 adopted DDR4 SDRAM PC4-34100, the highest transmission speed was 272.8Gbit/S, when nonvolatile memory 11' S data transmission interface adopted S-ATA 3.0 agreement, the highest transmission speed was 6Gbit/S, consequently, under this kind of condition, the utility model discloses a highest data storage speed is 6Gbit/S, to the storage of the whole section image of digital pathology of data volume about 32Gbit, the shortest storage time is about 5.3 seconds, because digital image output shows after, the user generally need observe, especially in digital pathology diagnostic process, the time of observing and diagnosing needs 20 seconds ( of the high-speed data storage time of the diagnosis like this utility model discloses a data storage time that the high speed is just like.

It should be noted that, in the case of no conflict, those skilled in the art may combine the technical features related to the above examples with each other according to practical situations to achieve corresponding technical effects, and details of various combining cases are not described in herein.

It is above only the utility model discloses a preferred embodiment, the utility model discloses a scope of protection does not only confine above-mentioned embodiment, the all belongs to the utility model discloses a technical scheme under the thinking all belongs to the utility model discloses a scope of protection. It should be noted that, for those skilled in the art, various modifications and decorations can be made without departing from the principle of the present invention, and these modifications and decorations should also be regarded as the protection scope of the present invention.

Claims

1, digital pathology imaging equipment, characterized by, including microscope objective (1), digital image sensor (2) and microscope illuminator (3);

the micro-lighting device (3) comprises a light source (101), a Mie scattering device (103), an optical cavity (102) and a condenser (105), wherein the light source (101) is located on the side of the Mie scattering device (103), the condenser (105) is located on the other side of the Mie scattering device (103), the Mie scattering device (103) is sleeved in the optical cavity (102), the light source (101) is used for emitting light to irradiate the Mie scattering device (103), the Mie scattering device (103) is used for emitting the light emitted by the light source (101) to irradiate the condenser (105), and the condenser (105) is used for focusing and outputting the light emitted by the Mie scattering device (103) to a measured body;

the microscope objective (1) comprises an th lens (502) and a second lens (505) which are sequentially arranged along the optical axis direction, the microscope objective (1) receives light incident from a detected object through a th lens (502), the surface of the th lens (502) facing an object plane (50) is a front surface, the surface facing an image plane (507) is a rear surface, the surface of the second lens (505) facing the object plane (50) is a front surface, and the surface facing the image plane (507) is a rear surface, the front surface of the th lens (502) is plated with a th semi-transparent and semi-reflective optical medium spectral film (501), and the rear surface of the second lens (505) is plated with a second semi-transparent and semi-reflective optical medium spectral film (506);

the digital image sensor (2) is used for receiving the light incident from the second lens (505) and performing digital imaging.

2. The digital pathology imaging apparatus of claim 1,

the number of the micro-lighting devices (3) is multiple, and the micro-lighting devices are sequentially arranged to form a micro-lighting device array;

the number of the micro objectives (1) is equal to that of the micro lighting devices (3) and corresponds to , so as to form an objective lens array;

the number of digital image sensors (2) is equal to the number of micro objectives (1) and corresponds to to form a sensor array.

3. The digital pathology imaging apparatus of claim 2,

the sensor array is used for sequentially arranging images formed by the digital image sensors (2) in a second direction without intervals when the sensor array moves along the th direction, and the th direction is perpendicular to the second direction.

4. The digital pathology imaging apparatus of claim 3,

the sensor array is provided with N rows which are arranged at intervals in parallel along the th direction, and N is an integer which is greater than or equal to 2;

the adjacent two rows are respectively an N1 th row and an N2 th row along the th direction, N2= N1+1, N1 is an integer greater than or equal to 1, the N2 th row is offset from the N1 th row along the second direction by a distance FoV, and the FoV is the size of an image formed by the digital image sensor (2) in the second direction.

5. The digital pathology imaging apparatus of claim 3,

the sensor array is provided with N rows which are arranged at intervals in parallel along the th direction, wherein N is an integer which is more than or equal to 3, the number of the digital image sensors (2) positioned in the two outermost rows in the sensor array is equal and M1, the number of the digital image sensors (2) in the other rows is M2, and M1= M2+ 1;

the adjacent two rows are respectively an N1 th row and an N2 th row along the th direction, N2= N1+1, N1 is an integer greater than or equal to 1, when N2 is smaller than N, the N2 th row is offset from the N1 th row along the second direction by a distance FoV, when N2 is equal to N, the N2 th row protrudes from the N1 th row along the second direction by a distance FoV, and the FoV is the size of an image formed by the digital image sensor (2) in the second direction.

6. The digital pathology imaging apparatus of claim 4 or 5,

the number of the digital image sensors (2) in each row is more than two, and the digital image sensors are sequentially arranged along the second direction;

two adjacent digital image sensors (2) in each row are equidistant in the second direction and are r 1.

7. The digital pathology imaging apparatus of claim 6,

n is the smallest integer greater than or equal to (W + r)/FoV;

r1=N*FoV-W；

wherein W is the dimension of the digital sensor along the second direction, and r is the minimum interval which can be realized by the processing technology of two adjacent digital image sensors (2) in the same rows in the second direction.

8. The digital pathology imaging apparatus of claim 6,

the spacing between two adjacent rows in the -th direction is r2, and r2 is the minimum spacing that can be achieved by the processing technology of the digital image sensors (2) in the two adjacent rows in the -th direction.

9. The digital pathology imaging apparatus according to any one of claims 2 to 5, 7 and 8, further comprising a fixing plate (61), wherein the fixing plate (61) is provided with a mounting hole (62);

the number of the mounting holes (62) is equal to that of the micro-objectives (1) and corresponds to , each micro-objective (1) is correspondingly mounted in the corresponding mounting hole (62), the th lens (502) is located at the end of the mounting hole (62), and the second lens (505) is located at the other end of the mounting hole (62).

10. The digital pathology imaging apparatus of claim 9,

the outer diameter of the th lens (502) is smaller than the outer diameter of the second lens (505);

the mounting hole (62) comprises an th hole section (601), a second hole section (602) and a third hole section (603) which are connected in sequence, and the outer diameters of the th hole section (601), the second hole section (602) and the third hole section (603) are reduced in sequence;

wherein the th lens (502) is fixed on the th hole segment (601), and the second lens (505) is fixed on the third hole segment (603).

11. The digital pathology imaging apparatus of claim 10,

a notch (621) is formed in the side wall of the hole segment (601), a photoresist (64) is filled in the notch (621), and the lens (502) is fixed on the hole segment (601) through the photoresist (64);

and/or a second gap (622) is arranged on the side wall of the third hole section (603), a light adhesive (64) is filled in the second gap (622), and the second lens (505) is fixed on the third hole section (603) through the light adhesive (64).

12. The digital pathology imaging apparatus of claim 11,

when a notch (621) is formed in the side wall of the -th hole segment (601) and a second notch (622) is formed in the side wall of the third hole segment (603), the notch (621) is located at the end, close to the second hole segment (602), of the -th hole segment (601), and the second notch (622) is located at the end, away from the second hole segment (602), of the third hole segment (603).

13. The digital pathology imaging apparatus of any one of claims 10 to 12, wherein,

the second hole section (602) is in a frustum shape, and the central line of the second hole section (602) is coincident with the central line of the th lens (502) or the second lens (505).

14. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the light source (101) is a light emitting diode or a semiconductor laser.

15. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the Mie scattering device (103) is solid optical devices distributed with Mie scattering medium particles (104), the optical devices are transparent or semitransparent, and the refractive index of the optical devices is smaller than that of the Mie scattering medium particles (104).

16. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the optical cavity (102) is a hollow cylindrical closed cavity which is wrapped outside the Mie scattering device (103) and is provided with openings at two ends, and the inner wall of the optical cavity is a mirror surface for reflecting light or the surface of a black oxidation layer.

17. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the condenser lens (105) is optical lenses or optical lens combinations capable of converging and irradiating uniform light in a converging direction.

18. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the light source (101) is fixed on the side of the Mie scattering device (103) through optical cement bonding, and the condenser lens (105) is fixed on the other side of the Mie scattering device (103) through optical cement bonding.

19. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the th lens (502) and the second lens (505) are circular lenses, and a gap is arranged between the th lens (502) and the second lens (505), wherein the gap is filled with air or liquid, or a lens and lens combination is arranged in the gap.

20. The digital pathology imaging apparatus of any one of claims 1 to 5, 7, 8, 10 to 12, wherein,

the front surface and the rear surface of the th lens (502) are aspheric, and the front surface and the rear surface of the second lens (505) are aspheric.

21. The digital pathology imaging apparatus according to any one of claims 1 to 5, 7, 8, 10 to 12, further comprising an image data acquisition controller (7), a data bus interface (8), a random access memory (9), a central processing unit (10), a non-volatile memory (11) and a display output port (12);

the digital image sensor (2) is connected with an image data acquisition controller (7) through a parallel data interface, and the image data acquisition controller (7) is used for reading digital image data transmitted by the digital image sensor (2); the image data acquisition controller (7) is connected with the random access memory (9) through a data bus interface (8), and the image data acquisition controller (7) transmits digital image data to the random access memory (9) through the data bus interface (8); the central processing unit (10) is connected with the random access memory (9), the nonvolatile memory (11) and the display output port (12) through a circuit bus, and the central processing unit (10) is used for reading the digital image data in the random access memory (9), storing the digital image data into the nonvolatile memory (11) and outputting the digital image data to the display output port (12) for displaying the image data.

22. The digital pathology imaging apparatus of claim 21,

the image data acquisition controller (7) and the central processing unit (10) are processor chips or electronic systems with serial computing and logic processing, or processor chips or electronic systems with parallel computing and logic processing, or processor chips or electronic systems with both serial and parallel computing and logic processing.

23. The digital pathology imaging apparatus of claim 21,

the data bus interface (8) is a data bus and hardware interface from the image data acquisition controller (7) to the random access memory (9).

24. The digital pathology imaging apparatus of claim 21,

the random access memory (9) is a register with data buffer access; and/or the nonvolatile memory (11) is a computer memory which can not disappear after the power supply is turned off.

25. The digital pathology imaging apparatus of claim 21,

the image data acquisition controller (7) is used for receiving the method or the communication protocol of the digital image sensor (2) in parallel or in series so as to acquire and process the image data, and adopts a serial or parallel data processing algorithm to pre-process the image data.

26. The digital pathology imaging apparatus of claim 21,

the random access memory (9) is used for writing the read bus interface data in a direct memory access manner.

27. The digital pathology imaging apparatus of claim 21,

the central processing unit (10) is used for reading the data stored in the random access memory (9) and writing the data read from the random access memory (9) into the display output port (12) in a direct memory access mode.

28. The digital pathology imaging apparatus of claim 21,

the nonvolatile memory (11) is used for reading the data stored in the random access memory (9) and writing the read data in the random access memory (9) in a direct memory access mode.