The invention is related to a method for measuring the height of a skin basal cell, comprising the following steps: providing a non-invasive microscopy device for shooting a picture of at least one skin basal cell of skin to be tested, including a laser source for emitting laser light with pulsed laser and an image processing element for processing image signals; converging the laser light to the skin to be tested via the image processing element and obtaining 2D images; utilizing the image processing element to stack the 2D images; labelling the first appearing 2D image of the at least one basal cell as a first layer; labelling the just disappearing 2D image of the at least one basal cell as a last layer; and multiplying the stacking number of the stacking images between the first layer and the last layer with a preset distance between two stacking images via calculation, thereby obtaining the height of the at least one basal cell for assessing of a skin pigmentation patient to be cured.

A light emitting device, an optical detection system, an optical detection device and an optical detection method, the light emitting device comprising: a light source (01), and an aperture limiting unit (03) located on an emergent light path of the light source (01); the light source (01) is used to emit light; and the aperture limiting unit (03) is used to limit the aperture of light emitted by the light source (01) when a current detection area of an object to be tested (05) has a high aspect ratio structure so as to block a portion of light having a large included angle with the normal direction of the object to be tested (05), such that the light is incident on the current detection area of the object to be tested (05) along the normal direction of the object to be tested (05) or along a direction that forms a small angle with the normal direction of the object to be tested (05). Thus, the high aspect ratio structure of the current detection area may be effectively detected.

An optical measurement system comprises a polarization beam splitter for dividing an incident beam into a reference beam and a measurement beam, a first beam splitter for reflecting the measurement beam to form a first reflected measurement beam, a spatial light modulator for modulating the first reflected measurement beam to form a modulated measurement beam, a condenser lens for focusing the modulated measurement beam to an object to form a penetrating measurement beam, an objective lens for converting the penetrating measurement beam into a parallel measurement beam, a mirror for reflecting the parallel measurement beam to form an object beam, a second beam splitter for reflecting the reference beam to a path coincident with that of the object beam, and a camera for receiving an interference signal generated by the reference beam and the object beam to generate an image of the object.

A modular confocal microscope includes a beam steering means arranged to direct the source of electromagnetic radiation non-collinearly with the optical axis of a focusing lens. The focused non-collinearly directed source of electromagnetic radiation is used for an imaging basis of targeted one or more sites of a specimen. An arrayed detector is configured along a beam path in a conjugate confocal plane to the targeted one or more sites of the specimen. The arrayed detector is also configured to provide autocorrection information to maintain focus and image quality of the targeted one or more sites using the imaging basis. The arrayed detector provides high-throughput configured synthetic apertures in a pixel range array of N=2×2 up to an array of N=21×21.

Measurement of the three dimensional morphology of blood cells is performed using a model for simulating reflectance confocal images of the cells, providing the relation between cell morphology and the resulting interference patterns under confocal illumination. The simulation model uses the top and bottom membranes of the cell as the elements for generating the interference fringes, and takes into account the cell size, shape, angle of orientation and distance from the focal point of the confocal illumination beam. By comparing the simulated cell images to actual interference patterns obtained in confocal images obtained from the blood samples, the model can be used for providing three dimensional measurements of the individual cell morphology. This enables, for instance, in vitro measurement of the mean corpuscular volume of blood cells and diagnosis of hematological disorders which are associated with cell morphology deviations, such as thalassemia and sickle cell anemia.

Measurement of the three dimensional morphology of blood cells is performed using a model for simulating reflectance confocal images of the cells, providing the relation between cell morphology and the resulting interference patterns under confocal illumination. The simulation model uses the top and bottom membranes of the cell as the elements for generating the interference fringes, and takes into account the cell size, shape, angle of orientation and distance from the focal point of the confocal illumination beam. By comparing the simulated cell images to actual interference patterns obtained in confocal images obtained from the blood samples, the model can be used for providing three dimensional measurements of the individual cell morphology. This enables, for instance, in vitro measurement of the mean corpuscular volume of blood cells and diagnosis of hematological disorders which are associated with cell morphology deviations, such as thalassemia and sickle cell anemia.

A method for mounting a sensor bearing unit providing a bearing and an impulse ring provided with a target holder and with a target mounted on an axial portion of the target holder. The method including measuring an eccentricity E.sub.1 between the target and the axial portion of the target holder, measuring an eccentricity E.sub.2 between a groove made in the bore of an inner ring of the bearing and the bore, introducing the target holder inside the groove, turning the target holder inside the groove to an angular position in which the eccentricity E.sub.total between the target and the bore of the inner ring is less than or equal to a predetermined value which is lower than the sum of the eccentricities E.sub.1 and E.sub.2, and securing the target holder inside the groove of the inner ring at the angular position.

Provided is a super-resolution holographic microscope including a light source configured to emit input light, a diffraction grating configured to split the input light into first diffracted light and second diffracted light, a mirror configured to reflect the first diffracted light, a wafer stage arranged on an optical path of the second diffracted light and on which a wafer is configured to be arranged, and a camera configured to receive the first diffracted light that is reflected by the mirror and the second diffracted light that is reflected by the wafer to generate a plurality of hologram images of the wafer.

An image sensor includes: a photoelectric conversion film that performs photoelectric conversion on light having entered therein; at least two electrodes, including a first electrode and a second electrode, disposed at a surface of the photoelectric conversion film; and at least two electrodes, including a third electrode and a fourth electrode, disposed at another surface of the photoelectric conversion film.

A system to generate image representations includes a first objective that receives a first light beam emitted from a sample and a second objective that receives a second light beam emitted from the sample, where the first light beam and the second light beam have conjugate phase. The system also includes a first diffractive element to receive the first light beam and separate it into a first plurality of diffractive light beams that are spatially distinct, and a second diffractive element to receive the second light beam and separate it into a second plurality of diffractive light beams that are spatially distinct. The system further includes a detector that receives the first and second plurality of diffractive light beams. The first plurality of diffractive light beams and the second plurality of diffractive light beams are simultaneously directed and focused onto different portions of an image plane of the detector.