WO2015133824A1 - Dispositif de balayage portable - Google Patents

Dispositif de balayage portable Download PDF

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Publication number
WO2015133824A1
WO2015133824A1 PCT/KR2015/002101 KR2015002101W WO2015133824A1 WO 2015133824 A1 WO2015133824 A1 WO 2015133824A1 KR 2015002101 W KR2015002101 W KR 2015002101W WO 2015133824 A1 WO2015133824 A1 WO 2015133824A1
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WIPO (PCT)
Prior art keywords
light
reflected
unit
portable scanner
output
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PCT/KR2015/002101
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English (en)
Korean (ko)
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이태경
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Individual
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0088—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for oral or dental tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient; User input means
    • A61B5/7475—User input or interface means, e.g. keyboard, pointing device, joystick
    • A61B5/7495—User input or interface means, e.g. keyboard, pointing device, joystick using a reader or scanner device, e.g. barcode scanner
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C9/00—Impression cups, i.e. impression trays; Impression methods
    • A61C9/004—Means or methods for taking digitized impressions
    • A61C9/0046—Data acquisition means or methods
    • A61C9/0053—Optical means or methods, e.g. scanning the teeth by a laser or light beam
    • A61C9/0073—Interferometric means or methods, e.g. creation of a hologram

Definitions

  • the present invention relates to a scanner for three-dimensional measurement of a large-scale surface (Meso-scale surface), such as a patient's teeth or skin, and more particularly to a portable scanner using a low-coherent interferometry It is about.
  • a large-scale surface such as a patient's teeth or skin
  • a plaster model (Master Model) is usually created based on the oral cavity, and a prosthesis is made based on the plaster model.
  • the manufacturing method using the plaster model as a mold has been traditional and has been progressed for a long time, so that the reliability and standardization are good, but it is difficult to match the error of the pulling process and the coma ratio of the impression material, and the curing time of the impression material depends on temperature and humidity. It was difficult to expect consistent results.
  • a material expressing a constant impression hardening condition such as a silicone impression material has a disadvantage that the cost burden of the patient is increased due to the high price, there is an inconvenience that does not fall well in the process of removing the impression material after curing in the oral cavity.
  • a method of irradiating a pattern light source in the oral cavity using a projector as a light source, acquiring it with a camera, and converting it into three-dimensional data using a triangular method has been applied.
  • the sharpness of Light Gradient is not high and there is a limit to increase the precision due to the light blurring with distance.
  • optical problems such as scattering and diffuse reflection of the light source in the process of directly receiving the pattern light source interfered with the accurate data reception, which caused a problem in accurate 3D reconstruction.
  • a confocal scanning method has been proposed to enable scanning without powder coating, but the manufacturing and assembly of a confocal disk (Nipkow Disk), which is a part of a confocal scanner, is relatively difficult and confocal method is used.
  • Embodiments of the present invention are to provide a miniaturized portable scanner capable of performing accurate three-dimensional modeling of tissue such as a patient's teeth or skin using the optical interference effect.
  • the portable scanner of the present invention includes: a light output unit to which a light source is irradiated; a light irradiation unit which generates a focus on the output light output from the light output unit and gives directionality to the output light; and the light irradiation unit A light splitter positioned at the front to guide the output light toward the front and the side; and an output light positioned at the front of the light splitter and guided through the light splitter toward the object to be measured in the oral cavity of the patient.
  • an image information acquisition unit receiving the light source re-reflected through the phase modulator and the light source reflected from the object to be measured.
  • the light output unit may be a multi-wavelength light source, and may be selected from one of a LED light, a high brightness diode, or a plurality of laser light sources.
  • the light irradiator may include a focus generator configured to generate a focus by aligning different wavelengths of the output light; And a first lens spaced apart in front of the focus generator to impart linearity to the output light.
  • the focus generator may include a green lens or an optical fiber or an aperture formed with a pinhole, a combination of an aperture formed with a green lens and a pinhole, or a combination of an optical fiber and an aperture formed with a pinhole, or a green lens and a pinhole. It may be selected from a combination of the aperture and the optical fiber formed.
  • the first lens may be a combination of a concave lens and a convex lens, or any one of a convex lens, a concave lens, or a parallel light lens.
  • the light splitter may be any one of a deposition coated flat glass, a deposition coated rectangular prism, or a deposition coated bonding prism.
  • the portable scanner of the present invention only the interference light generated when the reflected light reflected by the phase modulator and the reflected light reflected from the measured object cross each other or the reflected light reflected by the measured object to the image information acquisition unit. It may be configured to be selectively input.
  • the portable scanner may include a second lens positioned in front of the light splitter to diffuse the output light into an area corresponding to the first reflector.
  • the second reflector may include a first auxiliary reflector positioned on the light splitter to reflect output light split by the light splitter to the phase modulator; And a reflected light positioned below the light splitter and reflected from the object to be measured and split laterally through the light splitter, or reflected by the phase modulator and passed through the light splitter through a first auxiliary reflector.
  • One reflected light may include a second auxiliary reflector to guide the reflected light to the image information acquisition unit.
  • the portable scanner may include a third lens disposed between the first auxiliary reflector and the phase modulator and converting the reflected light reflected by the first auxiliary reflector into focused light. .
  • the phase modulator is moved to the front and rear at a constant speed by a transfer unit; and the reflected light formed on the front surface of the disk and reflected from the second reflector It may include a reflective surface; and a phase detection unit for detecting the amount or position of the front and rear movement of the disk.
  • the transfer unit for moving the disk forward and backward may include any one of a slope cam mechanism, an eccentric cam mechanism, a barrel cam mechanism, a twin rack and pinion mechanism or a single rack and pinion mechanism having an elastic member.
  • the portable scanner cuts off the output light split through the light splitter on the optical path between the phase modulator and the light splitter, and compares it to the image information acquisition unit for at least one of the phase modulation periods of the phase modulator.
  • a shielding part may be provided such that only interference light or reflection light reflected from the object to be measured is received.
  • the portable scanner is provided with an additional auxiliary light source other than the optical output unit, and the auxiliary light source is turned on for the at least one phase modulation period of the phase modulator in place of the optical output unit to be output to the object to be measured. It is also possible to receive only the reflected light of the auxiliary light source reflected from the object under measurement to the image information acquisition unit.
  • the phase modulator is in the form of a disk and rotates at a constant speed by a rotating unit; and a predetermined interval along the circumferential direction of the disk has a depth And a reflective surface positioned inside the depth changing unit and reflecting the reflected light reflected by the second reflecting unit.
  • the depth change part may include a non-reflective part on which at least one reflective surface is not formed.
  • the handheld scanner of the present invention may include a gripping portion that is held in the operator's hand, and an insertion portion that extends in front of the gripping portion and the first reflecting portion is installed at the distal end and inserted into the mouth of the patient.
  • the portable scanner may further include a protective cover detachably coupled to the insertion unit.
  • the portable scanner includes a connector that is rotatably connected freely, the scanner arm consisting of a multi-joint extension bar extending with a predetermined length from the connector, the scanner arm may be configured to be installed in the main body.
  • the portable scanner may further include an elastic pad inserted into the gripping groove and formed in a symmetrical shape to accommodate the operator's finger.
  • the portable scanner of the present invention controls the flashing state, the spacing, the wavelength and the brightness of the light output unit or the auxiliary light source, the operating state of the phase modulator, and whether the shielding unit is shielded, the speed and the period, And a control unit for synchronizing the image information acquired by the image information acquisition unit with the data received by the phase modulation unit and the position information received from the position information detection unit.
  • the portable scanner of the present invention may include a data processing module for calculating the data received by the control unit to process the 3D image information, and to map the color information of the object to be measured.
  • a portable scanner for acquiring accurate data on a patient's tooth treatment and shape, and modeling it in three dimensions can be used in a portable manner, thereby improving convenience and portability of the operator, and reflected light irradiated to the tooth. Since scattering is minimized, it is more convenient to measure the depth in mm.
  • FIG. 1 is a simplified view of a portable scanner according to an embodiment of the present invention.
  • FIGS. 2 to 6 are perspective views showing various embodiments of the phase shift unit of the forward and backward movement type included in the portable scanner of the present invention.
  • FIG. 7 is a perspective view showing an embodiment of a rotating disk type phase modulator included in the portable scanner of the present invention.
  • FIG. 8 is an installation perspective view showing a state in which the portable scanner is installed in accordance with an embodiment of the present invention.
  • FIG. 9 is a perspective view of a portable scanner according to an embodiment of the present invention.
  • 10 to 11 is an operating state diagram of a portable scanner according to an embodiment of the present invention.
  • FIG. 12 illustrates an example of a tooth (molar) in a state where optical interference is generated by a portable scanner according to an embodiment of the present invention.
  • FIG. 13 is a perspective view briefly illustrating a state in which a portable scanner transmits data in a wireless state according to an embodiment of the present invention.
  • the portable scanner 1 performs scanning by using an optical interference effect on a tooth, which is the object to be measured 10, and reduces the size of the portable scanner 1 to be convenient for the operator to use. You can create a model.
  • the portable scanner 1 includes a body portion 1a on which internal parts are fixed, and an insertion portion 1b extending forward of the body portion 1a and inserted into the mouth of the patient at the tip portion.
  • the body part 1a may be attached to the scanner arm in some cases, so that the operator may perform the procedure more conveniently.
  • Embodiments related thereto are illustrated in FIGS. 8 and 9.
  • the portable scanner 1 includes an elastic pad 5 inserted into the gripping groove 1d and formed in a symmetrical shape to accommodate the operator's finger, which is different from each other due to its inherent elasticity. Adapted to the user's hand having a size, it is easily gripped and comfortable to use, and because of the symmetrical shape, the grip is equally exerted on each of the left and right hands, and the portable scanner 1 Even if you need to turn 180 degrees, you can easily grip.
  • the gripping groove (1d) is formed in a symmetrical form in the left and right and up and down directions so that the elastic pad (5) on which the operator's finger is seated, the gripping groove (1d) is formed in this way Regardless of whether the operator is right-handed or left-handed, both can be used, thereby improving convenience and portability.
  • the gripping grooves 1d or the elastic pads 5 are formed symmetrically from side to side and up and down, so that the operator places the insertion part 1b of the portable scanner 1 in the forward direction by using the thumb and index finger 90 degrees or 180 degrees. Even in the case of rotating, the finger may be stably seated on the elastic pad 5.
  • the portable scanner 1 of the present invention can be connected to the connector (1c) connected to be freely rotatable in a state held by the operator, and again a predetermined length in the connector (1c)
  • the scanner arm 1e configured by connecting the extension bars 1d extending with each other in a joint may be installed in the main body 1f.
  • the portable scanner 1 is stably installed by the extension bar 1d to minimize noise generation due to shaking while scanning the oral cavity of the patient, thereby generating more accurate three-dimensional data.
  • the main body 1f may be connected to a chair on which the patient is seated, or may be a separate structure, and a separate structure that does not cause shaking may be used.
  • the light output unit 100 located inside the grip unit 1a and irradiated with a light source is output from the light output unit 100.
  • a second reflector 500 and a rear side of the second reflector 500 A phase modulator 600 for changing a light travel distance from the splitter 300 and an image information acquisition unit for receiving a light source reflected back through the phase modulator 600 and a light source reflected from the object to be measured ( 700).
  • the light output unit 100 may be selectively used as a broadband light source or a multi-wavelength light source, either a LED light or a high-brightness diode, or a mixed light source in which lasers of various wavelengths are mixed.
  • the broadband light source or the multi-wavelength light source may be different from each other. It means a light source that emits two or more photons having a wavelength.
  • the present embodiment is described as an LED light for convenience of description, but need not be limited thereto, and any form may be provided as long as it satisfies low coherence and high brightness among multi-wavelength light sources.
  • the color of the LED light may be white, but is not necessarily limited to the color.
  • the LED light is installed on a substrate having a predetermined size, and the substrate is operated by receiving power through a battery having a built-in power source or a power cable (not shown) extending out of the portable scanner 1.
  • the light irradiator 200 is positioned in front of the light output unit 100 and includes a focus generator 210 and a first lens 220.
  • the focus generator 210 may be one of a green lens or an optical fiber or an aperture in which a pin hole is formed or an aperture in which the green lens and a pin hole are formed so that a focus is generated by aligning different wavelengths of output light.
  • the combination or the combination of the optical fiber and the pinhole formed aperture or the combination of the green lens and the pinhole formed aperture and the optical fiber can be used.
  • the output light is irradiated toward the front with different wavelengths.
  • wavelengths are not aligned, so it is difficult to obtain accurate interference fringe data on the teeth of the patient, and thus a focus generator 210 is required.
  • an example in which an aperture 40 having a pinhole is provided as the focus generator 210 is illustrated.
  • the output light is irradiated forward after passing through the aperture 40, which is the focal generator 210, with its wavelength aligned to have coherence.
  • the output light passing through the aperture 40 is converted into parallel light having a constant width and irradiated toward the front.
  • the first lens 220 may be positioned in front of the focus generator 210 and may be fixed to the inside of the oral scanner 1 to impart straightness to the output light. Guide to 300.
  • the lens used as the first lens 220 may be a combination of a concave lens and a convex lens, or any one of a convex lens and a concave lens may be selectively used.
  • a telecentric lens may be used. It is noted that it is not necessarily limited to the lens, and it is also possible to use other lenses that can change the output light into the form of parallel light.
  • the light splitter 300 acquires the interference light generated when the reflected light reflected by the phase modulator 600 and the reflected light reflected by the object 10 to be described later cross each other, by the image information acquisition unit 700. To be installed.
  • the light splitter 300 has a structure in which one of the deposition-coated flat glass, the deposition-coated right angle prism, or the deposition-coated junction prism is in close contact with the inclined (for example, about 45 degrees) prism faces facing each other.
  • the output light is irradiated to the light splitter 300
  • a portion of the light splitter 300 is moved forward and reflected back after being irradiated to the object, and the rest of the phase modulator 600 passes through the second reflector 500 to be described later.
  • the optical interference region generated by the returned reflected lights is input to the image information acquisition unit 700 and stored as data about the teeth of the patient. A detailed description thereof will be described with reference to the second reflector 500. Let's do it.
  • the light splitter 300 is disposed in a direction facing the light output unit 100, and the fixed position is stably maintained by a separate position fixing member (not shown) that fixes the position.
  • the phase modulator 600 is configured to change the light travel distance in the direction toward the front or the rear with respect to the drawing, which is the first length (L1) with the tooth (object to be measured) in the light splitter 300,
  • the second length L2 from the light splitter 300 to the reflective surface 630 formed in the phase modulator 600 via the first auxiliary reflector 510 is the same length, optical interference occurs.
  • the first and second lengths L1 and L2 do not match, optical interference does not occur.
  • the phase modulator 600 includes a movement type that is moved forward and backward with respect to the longitudinal direction inside the oral cavity scanner 1, and a rotation type that is rotated in a fixed position by the rotation unit to form a second length ( By causing a change in L2), it is possible to obtain optical interference according to a distance, thereby obtaining interference fringe data capable of three-dimensional reconstruction.
  • a movement type that is moved forward and backward with respect to the longitudinal direction inside the oral cavity scanner 1
  • a rotation type that is rotated in a fixed position by the rotation unit to form a second length
  • phase modulator 600 Although various embodiments of the phase modulator 600 vary in mechanical mechanisms for changing the light travel distance, the basic principles of using the phase modulator 600 are the same. That is, the reflection surface 630 is formed in all the phase modulators 600, and the phase detection unit 650 detects different positions according to the movement of the reflection surface 630, and transmits the result to the controller 800. And the phase shift data input to the controller 800 is received from the image information acquisition unit 700 and the position information detection unit 1000 of the portable scanner and the portable scanner for the object to be measured. Synchronized with the location information data to know the relative position of the, it is used as data for generating a three-dimensional scanning model for the patient's teeth.
  • the second lens 20 is positioned in front of the light splitter 300 to diffuse the output light via the light splitter 300 to the first reflector 400.
  • the first reflector 400 is positioned to be spaced apart from the front of the second lens 20 by a predetermined distance or more, and a 45 degree inclined mirror or a reflective prism is selectively used to reflect the output light to the teeth of the patient.
  • the first reflector 400 is located in the mouth of the patient and irrespective of the size of various teeth having different sizes, the light reflects the output light by being made larger than the size of the tooth so that the output light is irradiated to the teeth.
  • the second reflector 500 includes a first auxiliary reflector 510 and a second auxiliary reflector 520, and the first auxiliary reflector 510 is positioned above the light splitter 300.
  • the output light split by the light splitter 300 is reflected to the phase modulator 600.
  • the second auxiliary reflector 520 is positioned below the light splitter 300 and reflected from the object 10 to be reflected and split through the light splitter 300 or the phase modulator ( The reflected light reflected by 600 and passing through the light splitter 300 via the first auxiliary reflector 510 is induced to be reflected by the image information acquirer 700.
  • the first auxiliary reflector 510 and the second auxiliary reflector 520 are positioned to face each other on the upper and lower sides of the light splitter 300, respectively, and the reflective prism or mirror inclined at 45 degrees is provided. It is used to reflect the reflected light toward the rear.
  • the portable scanner 1 is disposed between the first auxiliary reflector 510 and the phase modulator 600 to concentrate the reflected light reflected by the first auxiliary reflector 510 on the phase modulator 600. It comprises a third lens 30 to switch to.
  • the image information acquisition unit 700 is advantageous in terms of using a conventional CCD camera, a camera having other characteristics may be selectively installed.
  • the data processing module 900 may perform phase modulation from the light splitter 300 by interfering fringes or interference light generated by the reflected light reflected by the phase modulator 600 by the light splitter 300.
  • a bright area is displayed by using an optical property that occurs only in a region where the movement path length up to the portion 600 and the optical movement path length from the light splitter 300 to the object are displayed as relatively high (Intensity) regions.
  • the image area is converted into two-dimensional coordinates such as X and Y, and the phase change value received by the phase modulator 600 is converted into a coordinate unit such as Z to calculate the result.
  • the individual three-dimensional image implemented from the image data having a bright area and the phase change value is expanded or matched based on the position information data acquired by the position information detector 1000, and as a result, the three-dimensional image of the entire object. You can implement the data.
  • the portable scanner 1 includes a position information detector 1000 for detecting a relative change in position of the portable scanner 1 with respect to the measurement target during the scanning process, and the position information detector 1000 includes a gyro sensor or It may be composed of any one or a combination of two or more of the geomagnetic sensor or the acceleration sensor.
  • the control unit 800 blinks the light output unit 100, blinks the time interval of the light output unit 100, whether the wavelength and phase modulation unit 600 of the light output unit 100, and phase modulation
  • the operating speed of the unit 600 and the phase value received from the phase modulator 600, the position change value received from the position information detector 1000, whether the image information acquirer 700 is acquired, and the image information acquirer may be controlled.
  • the controller 800 may synchronize the control target value with the image information acquired from the image information acquisition unit 700, and the synchronized information may be converted to be integrated and transmitted in a minimum signal form.
  • the portable scanner 1 calculates the data received from the control unit 800, performs matching and modeling with the 3D image information, and additionally maps the color information of the target object 10 to the modeling data. It may also include a data processing module 900.
  • the portable scanner 1 of the present invention blocks the output light split through the light splitter 300 while being provided on the optical path between the phase modulator 600 and the light splitter 300, thereby modulating the phase.
  • Non-interfering light or color information of the object 10 to be received is received by the image information acquisition unit 700 for at least one of the phase modulation periods of the unit 600 so that the surface color image information of the object to be measured 10 is received.
  • the shield 4 may be used in conjunction with the phase modulator 600 or may be independently controlled by the controller 800.
  • the portable scanner 1 may separately include an auxiliary light source 101 as shown in FIGS. 10 and 11, for at least one of the phase modulation periods of the phase modulator 600 or the phase. Regardless of the modulation period, the power of the light output unit 100 is cut off and the auxiliary light source 101 is turned on so that the reflected light of the auxiliary light source 101 is received by the image information acquisition unit 700. It is also possible to obtain surface color image information.
  • the auxiliary light source 101 may be provided separately inside or outside the insertion unit 1b or may be provided on the side of the light splitter 300 or between the light splitter 300 and the first reflector 400.
  • the portable scanner 1 of the present invention can be used as an oral camera as well as proceeding with color mapping to the three-dimensional scanning model.
  • the phase modulator 600 may be configured as a movement type that is moved forwards and backwards based on the longitudinal direction inside the oral cavity scanner 1, and a rotation type that is rotated at a proper position by the rotation unit.
  • a movement type that is moved forwards and backwards based on the longitudinal direction inside the oral cavity scanner 1, and a rotation type that is rotated at a proper position by the rotation unit.
  • the configuration of the "disk 610" used in the description of the various phase modulator 600 of the present invention is a moving object having a reflective surface 630 is formed despite the meaning of the disk shape commonly understood in the term. It is important to note that it is used generically.
  • the disk 610 is moved forward and backward at a constant speed by the transfer unit 601, and is formed on the front surface of the disk 610. And a reflection surface 630 for reflecting back the reflected light reflected by the second reflection unit, and a phase detection unit 650 for detecting the amount of forward and backward movement or position of the disk.
  • the transfer part 601 is inserted into the motor shaft installed in the motor 601a and has a slope cam 601b having an inclined surface inclined in one direction, and the slope cam 601b is inserted.
  • One end is supported on the inclined surface of the inclined cam 601b and is extended to the outside of the case 601c and is supported by an elastic member 601e installed at the other end thereof to the inclined cam 601b.
  • It includes a sliding member 601d which is moved in the front and rear directions.
  • the elastic member 601e is positioned in front of the disk 610 to generate a reciprocating transfer restoring force for the disk 610.
  • the spring is limited to using a coil spring, but another spring for which elastic restoring force is generated is used. Note that it is also possible.
  • the slope cam 601b is formed in a cylindrical shape, and an inclined surface is formed on the front surface thereof, so that the sliding member 601d is positioned in surface or point contact with the inclined surface, and is always tethered to the inclined surface by the elastic member 601e. State is maintained.
  • the sliding member 601d When the slope cam 601b is rotated, the sliding member 601d is moved forwards or backwards toward the elastic member 601e by the inclined surface, and is partially inserted into the case 601c, so that the sliding member 601d is stably moved without departing from the outside. .
  • phase modulator an example of configuring the transfer unit using the eccentric cam 601g is illustrated in FIG. 3.
  • the embodiments of FIGS. 3 to 6 will be described based on the configuration of the transfer unit having a different structure, the reflective surface 630 for re-reflecting the reflected light reflected from the motor 601a or the second reflecting unit, Descriptions or illustrations of common configurations, such as the phase detection unit 650 for detecting the amount of forward and backward movement or the position of the disk 610, or other techniques known to those skilled in the art may be omitted.
  • the phase modulator 600 includes an eccentric cam 601g receiving a rotational force of a motor (not shown), and a disk 610 positioned in contact with the eccentric cam 601g.
  • the eccentric cam 601g Since the eccentric cam 601g is inserted at the position where the motor shaft is eccentric, when the eccentric cam 601g is rotated, the disk 610 is moved in the front and rear direction as shown by the arrow, and the relative distance to the tooth is changed. do.
  • phase modulator 600 using the barrel cam 601h as a further embodiment using the cam.
  • the barrel cam 601h is formed by forming a helical groove 601i on the surface of the cylindrical body.
  • a guide pin 601j fixed to the disk 610 which is a driven body, is fitted in the groove 601i.
  • the guide pin 601j moves along the shape of the groove 601i, and as a result, the disk 610 moves in the front-rear direction.
  • a guide member for limiting the movement of the follower disk 610 in the front-rear direction should be provided.
  • the amount of forward and backward movement of the disk 610 according to the rotation angle of the barrel cam 601h depends on the profile of the helical groove 601i on the surface of the cylindrical body, and the rotation angle of the barrel cam 601h for convenience of control. It may be advantageous to simplify the back and forth movement of the disk 610 to have a linear change. This means that when the cylindrical surface of the barrel cam 601h is represented in a rectangular development view, the profile of the groove 601i appears as a straight line with a certain angle on the development view, wherein the slope of the straight line representing the profile of the groove 601i is The amount of forward and backward movement of the disk 610 according to the rotation angle of the barrel cam 601h is determined.
  • phase modulator 600 is configured as a movement type
  • the embodiment in which the phase modulator 600 is configured as a movement type may be implemented as a gear type in addition to the cam type, and such an embodiment is illustrated in FIGS. 5 and 6.
  • a twin rack and pinion type in which a second spur gear 601l which is a pair of driven gears to a first spur gear 601k that is a drive gear coupled to a motor shaft of the motor 601a. ) Is engaged with each other by 180 degrees, and the third spur gear 601m formed on the axis of the second spur gear 601l is disposed on the rack 601n and the rack provided 180 degrees to face the disk 610 side, respectively.
  • the phase modulator 600 moves forward and backward when the motor 601a rotates forward and backward.
  • the spur gear is shown and described as being applied to the embodiment of the present invention, the helical gear may be applied.
  • the gear type phase modulator 600 may be implemented as a rack and pinion type having the elastic member of FIG. 6.
  • one rack 601n is basically provided on the disk 610, and the pinion 601o engaged with the rack 601n has a rack and pinion structure connected to the motor 601a.
  • Similar to the embodiment of the present invention may be referred to as a single rack and pinion type, in this embodiment of the rack 601h in some sections of the rotation period as there is an unformed flat section on the one end of the pinion (601o). Since the teeth may be released, the elastic member 601e may be installed on one side of the disk 610 (opposite side on which the reflective surface is formed) to restore the initial position of the phase modulator 600.
  • the single rack and pinion type transfer unit coupled to the elastic member 601e of FIG. 6 forms a planar section in which a gear is not formed in a section of the pinion 601o so that the planar section is formed at the end of the rotation of the pinion 601o.
  • the rack (601h) is configured to quickly and automatically return the disk 610 to the initial position by the elastic force of the elastic member (601e).
  • phase modulator 600 according to another embodiment of the present invention is shown in Figure 7 the rotation type is rotated in place by the rotation unit.
  • the phase modulator 600 includes a disk 610 formed in a disk shape and rotated at a constant speed by the rotating unit 602, wherein the disk 610 is circumferentially aligned. It is characterized in that it comprises a reflective surface 630 which is located inside the depth change unit 620 having a predetermined interval with a predetermined interval to re-reflect the reflected light reflected by the second reflector 500.
  • the disk 610 is formed with a plurality of reflecting surfaces 630 along the circumferential direction, the depth of the reflecting surface 630 is made to become deeper along the clockwise or counterclockwise direction by the disk 610
  • the light interference effect may be caused by causing a change in the second distance L2 without moving in the front-rear direction.
  • the depth change unit 620 is disposed at a predetermined interval in a circumferential direction with respect to the center of the disk 610, but the reflective surface 630 is positioned to face the first auxiliary reflector 510. The reflected light reflected through the first auxiliary reflector 510 may be reflected again.
  • the reflective surface 630 may be any one of a reflective lens or a reflective film is selectively used, and may be changed to a configuration other than the above-described configuration.
  • the plurality of depth change parts 620 may include at least one non-reflective part 640.
  • the reflective surface is not formed in the non-reflective part 640, and the actual formation information of the tooth is input to the controller 800.
  • the disk 610 is rotated at a predetermined speed by the rotating unit 602.
  • the non-reflective unit 640 reflects only n of the plurality of reflecting surfaces 630 disposed along the circumferential direction of the disk 610. Since 630 is not formed, a color image of the measurement target object 10 without optical interference is input to the image information acquisition unit 700 every time the first rotation of the disc 610 is made to the controller 800. .
  • rotating unit 602 may be a conventional motor, but other configurations may be used to rotate the disk 610.
  • the operator can hygienically use the portable scanner 1 by coupling a new protective cover 3 to the inserting portion 1b for each patient, wherein the first reflecting portion 400 is used.
  • the surface of the protective cover 3 corresponding to is open.
  • the protective cover 3 When the operator wants to use the portable scanner 1, the protective cover 3 is removed or replaced outside of the insertion part 1b, and then the thumb, the index finger, and the middle finger are placed on the elastic pad 5 to be gripped stably. .
  • the elastic pad 5 may be used more conveniently because the thumb, the index finger, and the middle finger are seated even when the operator grips the portable scanner 1 in any direction.
  • the output light is moved to the second lens 20 and the first reflecting unit 400 via the light splitting unit 300, the output light is shown in the state shown in the drawing by the inclination angle of the first reflecting unit 400.
  • the output light irradiated toward the patient's tooth, and the output light irradiated onto the tooth is re-reflected and then moved to the light splitter 300 via the first reflector 400.
  • the reflected light is irradiated onto the disk 610 of the phase modulator 600 via the first auxiliary reflector 510 and the third lens 30 and is reflected back to the reflective surface 630 formed on the disk 610. Move toward the first auxiliary reflector 510.
  • the disk 610 is moved back and forth by the conveying part 601 or rotated at a predetermined speed by the rotating part 602, whereby the above-described first length (L1) and second length (L2) between each other.
  • the optical interference data may be received by different matching intervals, in which optical interference is detected only for an area of the measurement object having the same (or nearly the same) length as the first length L1 and the second length L2, In the other mismatched region, optical interference is not detected.
  • the interference light occurs even when the first length L1 and the second length L2 are in multiples of the wavelength, and the interference pattern occurs in a pattern such as a contour line or a straight line.
  • This can be a problem of phase ambiguity or parasitics.
  • the case of the optical interference can more accurately determine the length.
  • a low-coherent light is used.
  • a light source in which light of various wavelengths is mixed is applied, such as white light.
  • a multi-wavelength light source in which an LED, a high brightness diode, or a plurality of laser light sources are mixed may be used, but is not limited thereto.
  • interference light is generated only in a phase modulation section where the first length L1 and the second length L2 coincide or nearly coincide with each other, which is represented by relative brightness of light. That is, the portion where the optical interference occurs is shown as a high intensity region, and this characteristic makes the calculation easier to perform than an interferometer based on a single wavelength calculated using only the pattern shape of the interference fringe.
  • the operator may input the scanning data about the tooth to the controller 800 while moving the inserting portion 1b to various locations around the tooth in order to obtain more accurate 3D scanning data about the patient's teeth.
  • the reflected light is inputted to the image information acquisition unit 700 via the first auxiliary reflector 510, the light splitter 300, and the second auxiliary reflector 520, and moves along the movement of the portable scanner 1.
  • the movement displacement is input to the controller 800 through the position information detector 1000 and then used to match the image information data through the data processor.
  • various optical interference fringe areas are generated in the form of a mixture of contour lines or straight lines when optical interference is generated.
  • the area may be regarded as an X and Y coordinate value in the 2D photographic image, and the movement value of the phase modulator 600 may be converted into a Z coordinate value as a depth value with respect to the object to be measured. Three-dimensional modeling is generated for.
  • FIG. 12 (a) corresponds to a different depth relative to the black portion, and the depth difference may be regarded as the moving distance of the phase modulator moved during the time difference in which image information is acquired.
  • FIG. 12B is a diagram illustrating a shape in which three-dimensional modeling of FIG. 12A is performed as an example.
  • the image information obtaining unit 700 receives image information that does not generate an interference fringe.
  • the three-dimensional modeling may be realized.
  • a separate auxiliary light source 101 is provided, and the power of the light output unit 100 is supplied to at least one of the phase modulation periods of the phase modulation unit 600 or irrespective of the phase modulation period. It is also possible to block and turn on the auxiliary light source 101 so that the reflected light of the auxiliary light source 101 is received by the image information acquisition unit 700 so that the surface color image information of the object to be measured 10 can be acquired.
  • the portable scanner 1 may be connected to a server or a computer main body in a wireless manner, and in this case, through the wireless communication module 50 installed in the portable scanner 1.
  • Wireless connection can be used to more conveniently transmit the data on the patient's mouth.
  • the present invention is suitable for use as a portable scanner for acquiring accurate data on the treatment and shape of a patient's teeth and modeling it in three dimensions.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Physics & Mathematics (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Optics & Photonics (AREA)
  • Epidemiology (AREA)
  • Audiology, Speech & Language Pathology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Dental Tools And Instruments Or Auxiliary Dental Instruments (AREA)
  • Length Measuring Devices By Optical Means (AREA)

Abstract

L'invention concerne un dispositif de balayage portable qui comporte : une unité de sortie de lumière, par laquelle est émise la lumière ; une unité d'émission de lumière pour générer un foyer pour la lumière de sortie, qui est fournie par l'unité de sortie de lumière, et pour attribuer une orientation pour la lumière de sortie ; une unité de division de lumière située en face de l'unité d'émission de lumière pour guider la lumière de sortie vers l'avant et un côté ; une première unité de réflexion située en face de l'unité de division de lumière pour réfléchir la lumière de sortie guidée à travers l'unité de division de lumière vers un objet à mesurer, qui est disposé dans la cavité buccale d'un patient ; une seconde unité de réflexion disposée autour de l'unité de division de lumière pour réfléchir la lumière réfléchissante, qui est réfléchie par l'objet à mesurer à travers la première unité de réflexion, ou la lumière de sortie, qui est guidée vers le côté par l'unité de division de lumière, vers l'arrière ; une unité de modulation de phase disposée derrière la seconde unité de réflexion pour varier la distance de déplacement de la lumière à partir de l'unité de division de lumière ; une unité d'acquisition d'informations d'image pour recevoir à nouveau la lumière réfléchie à travers l'unité de modulation de phase et la lumière réfléchie par l'objet à mesurer.
PCT/KR2015/002101 2014-03-04 2015-03-04 Dispositif de balayage portable Ceased WO2015133824A1 (fr)

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KR1020140025485A KR101533341B1 (ko) 2014-03-04 2014-03-04 휴대형 스캐너
KR10-2014-0025485 2014-03-04

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113712698A (zh) * 2021-09-07 2021-11-30 苏州喆安医疗科技有限公司 一种分层可抛弃式口腔数字印模仪扫描头
EP4424273A4 (fr) * 2021-10-29 2025-02-05 Arcreal Inc. Scanner intra-buccal
EP4424272A4 (fr) * 2021-10-29 2025-02-05 Arcreal Inc. Scanner intra-buccal
EP4450022A4 (fr) * 2021-12-15 2025-10-01 Arcreal Inc Scanner intra-buccal

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102018211369B4 (de) * 2018-07-10 2021-06-24 Sirona Dental Systems Gmbh Optisches Messverfahren sowie optische Messvorrichtung
KR102341890B1 (ko) * 2021-02-01 2021-12-20 전승현 구강 스캐너
US20240197162A1 (en) * 2021-04-14 2024-06-20 Medit Corp. Hand-held scanner
KR20230062444A (ko) * 2021-10-29 2023-05-09 아크리얼 주식회사 구강 스캐너
EP4201372B1 (fr) * 2021-12-22 2024-10-09 3Shape A/S Scanner comprenant un nouveau mécanisme d'entraînement de lentille
KR102843675B1 (ko) * 2022-02-23 2025-08-07 주식회사바텍 구강 스캐너 및 이의 영상 데이터 획득 방법
US20250194913A1 (en) * 2022-02-23 2025-06-19 Vatech Co., Ltd. Intraoral scanner and method for obtaining image data therefrom
WO2025100831A1 (fr) * 2023-11-06 2025-05-15 아크리얼 주식회사 Scanner intra-buccal
KR20250089272A (ko) * 2023-12-11 2025-06-18 아크리얼 주식회사 구강 스캐너

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009018172A (ja) * 2008-08-04 2009-01-29 J Morita Tokyo Mfg Corp 歯科光診断装置
JP2011024797A (ja) * 2009-07-27 2011-02-10 Panasonic Corp 口腔内撮像装置
KR101043976B1 (ko) * 2009-12-15 2011-06-24 데오덴탈 주식회사 구강용 스캐너
JP2012000132A (ja) * 2010-06-14 2012-01-05 Olympus Corp う蝕観察装置

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009018172A (ja) * 2008-08-04 2009-01-29 J Morita Tokyo Mfg Corp 歯科光診断装置
JP2011024797A (ja) * 2009-07-27 2011-02-10 Panasonic Corp 口腔内撮像装置
KR101043976B1 (ko) * 2009-12-15 2011-06-24 데오덴탈 주식회사 구강용 스캐너
JP2012000132A (ja) * 2010-06-14 2012-01-05 Olympus Corp う蝕観察装置

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113712698A (zh) * 2021-09-07 2021-11-30 苏州喆安医疗科技有限公司 一种分层可抛弃式口腔数字印模仪扫描头
CN113712698B (zh) * 2021-09-07 2024-01-05 苏州喆安医疗科技有限公司 一种分层可抛弃式口腔数字印模仪扫描头
EP4424273A4 (fr) * 2021-10-29 2025-02-05 Arcreal Inc. Scanner intra-buccal
EP4424272A4 (fr) * 2021-10-29 2025-02-05 Arcreal Inc. Scanner intra-buccal
EP4450022A4 (fr) * 2021-12-15 2025-10-01 Arcreal Inc Scanner intra-buccal

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