Patent Publication Number: US-8971999-B2

Title: Intra-oral scanner

Description:
This application claims priority to Korean Patent Application No. 10-2009-0124780 filed on Dec. 15, 2009, which is incorporated herein by reference in their entirety. 
     TECHNICAL FIELD 
     The present disclosure relates to an intra-oral scanner, in particular, to an intra-oral scanner, which is inserted into a patient&#39;s oral cavity to scan the patient&#39;s teeth. 
     BACKGROUND ART 
     In general, dental hospitals or the like have performed medical cures and treatments to patients&#39; affected parts through impression taking that prepares plaster casts for the patients&#39; teeth. However, in the impression taking process, there have been problems, e.g., consumption of materials, cross-infection, possibility of damage to prepared casts, and preservation difficulties. 
     As a conventional method widely used to see the state of a patient&#39;s oral cavity, there has been a method of inserting a sheet-shaped film into the patient&#39;s oral cavity, fixing the film in the proximity of the patient&#39;s affected part by using the patient&#39;s hand or tongue, projecting a radiation ray such as an X-ray onto the affected part of the oral cavity, and using the film obtained from the projection. 
     However, since the conventional method depends on measurement through two-dimensional manual works using radiographs, or computer tomography (CT), errors may occur in the process of two-dimensional plane measurement of a three-dimensional structure. Further, a large amount of radiation rays are projected to a patient. Patients would have a financial burden. Complicated trial stages may cause various critical problems. 
     Accordingly, there has been a demand for an intra-oral scanner, which reduces the possibility of causing any problems in patients&#39; physical conditions and exactly accomplishes three-dimensional modeling of patients&#39; teeth. 
     DISCLOSURE OF THE INVENTION 
     Problems to be Solved by the Invention 
     In an illustrative embodiment, there is provided an intra-oral scanner, which is inserted into a user&#39;s oral cavity in a contactless manner to scan the user&#39;s teeth and generates three-dimensional scanning model. 
     Means for Solving the Problems 
     In accordance with an example of an illustrative embodiment, there is provided an intra-oral scanner including: an optical output unit, which outputs an output light; an optical output control unit, which rotates the optical output unit along a first reference axis or moves the optical output unit in left and right directions so as to control an emission position of the output light; an optical system, which reflects the output light with the emission position controlled by the optical output control unit to a tooth or teeth being scanned; an optical system driving unit, which rotates the optical system along a second reference axis vertical to the first reference axis so as to control a reflection angle of the output light; a guide, which guide the optical system to move within a preset distance from the optical output unit; an optical sensing unit, which senses the light reflected by the optical system at the tooth or teeth being scanned and converts the sensed light into an electrical signal; and a data transmitting unit, which transmits information of the electrical signal, information of the emission position of light and information of the reflection angle to a three-dimensional data generating unit to generate three-dimensional scanning model for the tooth or teeth being scanned. 
     In accordance with an example of an illustrative embodiment, there is provided an intra-oral scanner including: an optical output unit, which outputs an output light; a first optical system, which reflects the output light outputted from the optical output unit; a second optical system, which reflects the output light reflected through the first optical system to a tooth or teeth being scanned; a first optical system driving unit, which rotates the first optical system along a first reference axis or moves the first optical system in left and right directions so as to control an emission position of the output light; a second optical system driving unit, which rotates the second optical system along a second reference axis vertical to the first reference axis so as to control a reflection angle of the output light; a guide, which guides the second optical system to move within a preset distance from the optical output unit; an optical sensing unit, which senses the light reflected by the second optical system at the tooth or teeth being scanned and converts the sensed light into an electrical signal; and a data transmitting unit, which transmits information of the electrical signal, information of the emission position of light and information of the reflection angle to a three-dimensional data generating unit to generate three-dimensional scanning model for the teeth being scanned. 
     Effect of the Invention 
     With the above-described technical means of the illustrative embodiment, the intra-oral scanner is inserted into a patient&#39;s oral cavity to scan the patient&#39;s teeth in a contactless manner. Thus, three-dimensional data for the patient&#39;s teeth can be exactly measured. 
     With the above-described technical means of the illustrative embodiment, three-dimensional scanning is accomplished by using a light source that does not adversely affect the human body. Thus, patients&#39; teeth can be scanned without affecting the patients&#39; health. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Non-limiting and non-exhaustive embodiments will be described in conjunction with the accompanying drawings. Understanding that these drawings depict only several embodiments in accordance with the disclosure and are, therefore, not to be intended to limit its scope, the disclosure will be described with specificity and detail through use of the accompanying drawings, in which: 
         FIG. 1  is a plane view of an intra-oral scanner in accordance with an illustrative embodiment; 
         FIG. 2  is a block diagram showing configuration of an intra-oral scanner in accordance with an illustrative embodiment; 
         FIG. 3  is a side view of an intra-oral scanner in accordance with an illustrative embodiment; 
         FIG. 4  is a plane view of an intra-oral scanner in accordance with another illustrative embodiment; 
         FIG. 5  is a block diagram showing configuration of an intra-oral scanner in accordance with another illustrative embodiment; and 
         FIG. 6  is a side view of an intra-oral scanner in accordance with another illustrative embodiment. 
     
    
    
     BEST MODE FOR CARRYING OUT THE INVENTION 
     Hereinafter, illustrative embodiments will be described in detail with reference to the accompanying drawings so that inventive concept may be readily implemented by those skilled in the art. However, it is to be noted that the present disclosure is not limited to the illustrative embodiments and can be realized in various other ways. In the drawings, certain parts not directly relevant to the descriptions of the present disclosure are omitted to enhance the clarity of the drawings. Throughout this document, like reference numerals denote like parts. 
       FIG. 1  is a plane view of an intra-oral scanner in accordance with an illustrative embodiment. 
       FIG. 2  is a block diagram showing configuration of an intra-oral scanner in accordance with an illustrative embodiment. 
       FIG. 3  is a side view of an intra-oral scanner in accordance with an illustrative embodiment. 
     As illustrated in  FIGS. 1 and 3 , an intra-oral scanner  100  in accordance with an illustrative embodiment includes an insertion body  10 , a body  20 , a guide  30 , an optical system  40 , an optical system driving member  50 , an optical output device  60 , an optical sensing device  70 , a control module  80 , and a data processing module  90 . 
     A frame of the insertion body  10  is in a shape of an insertion tube projected from the body  20  so as to be inserted into the user&#39;s oral cavity. The frame may have five surfaces, which include one top surface, two side surfaces, one front surface, and one bottom surface. 
     The bottom surface of the insertion body  10  includes a light transmission window, which enables a scanning light source (e.g., a “laser light” in an illustrative embodiment) to be projected onto the tooth or teeth. 
     The top surface of the insertion body  10  is in parallel with the direction that the insertion body  10  is inserted into the oral cavity. The bottom surface has a certain angle to the top surface. Accordingly, the two surfaces may be formed to become large as they are close to the body  20 . This configuration is intended to protect light sources by securing a heading path of a light source outputted to the optical system  40  through the inside of the insertion body  10  and a light source reflected from the tooth or teeth and incident to the optical sensing device  70  through the optical system  40 . 
     In the inside of the insertion body  10 , the optical system  40  is connected to the guide  30  through the optical system driving member  50  such that the optical system  40  reflects a light source (hereinafter, referred to as “output light”) outputted from the optical output device  60  to be projected to the tooth or teeth and reflects an incident light source reflected from the tooth or teeth (hereinafter, referred to as “incident light”) to the optical sensing device  70 . 
     In this case, the guide  30  supports the optical system  40  to be connected to the inside of the insertion body  10 . The guide  30  controls a rolling member (not illustrated) connected to a motor (not illustrated) or others under a command from the control module  80  to move the optical system  40  forwardly and backwardly in the horizontal direction that the insertion body  10  is inserted. The optical system driving member  50  rotates the optical system  40  along a first reference axis under a command from the control module  80  so as to change an emission angle of the output light. The first reference axis is consistent with an A axis illustrated in  FIG. 1 . 
     Provided in the inside of the body  20  are the optical output device  60 , the optical sensing device  70 , the control module  80 , and the data processing module  90 . The optical output device outputs a light source to the optical system  40 . The optical sensing device  70  receives a light source reflected from the optical system  40 . The control module  80  controls driving of each of the optical system  40  and the optical output device  60  and processes output data of the optical sensing device  70 . The data processing module  90  generates three-dimensional data by using the data processed through the control module  80 . 
     The optical output device  60  in accordance with an illustrative embodiment is rotated based on a second reference axis so as to change an emission angle of the output light. The second reference axis is vertical to the first reference axis and consistent with a C axis illustrated in  FIG. 1 . The optical output device  60  moves in left and right directions (i.e., the A axis in  FIG. 1 ) in a sliding manner so as to change an emission position of the output light. 
     In an illustrative embodiment, a laser diode is described as an example of the optical output device  60 . For restriction of a size, an optical output device, which is as small as possible, may be used. The optical sensing device  70  may be a light receiving device such as a charged coupled device (CCD) or a position sensitive device (PSD). In an illustrative embodiment, a PSD is described as an example of the optical sensing device  70 . 
     Hereinafter, a teeth modeling method through three-dimensional scanning by the intra-oral scanner  100  in accordance with an illustrative embodiment will be described with reference to  FIGS. 2 and 3 . 
     With respect to the configuration of the intra-oral scanner  100  in accordance with an illustrative embodiment in  FIGS. 1 and 3 ,  FIG. 2  illustrates a block diagram for a data measurement unit  210 , a data measurement control unit  220 , and a data processing unit  230  based on data to be processed. 
     The configuration units in accordance with an illustrative embodiment in  FIG. 2  mean software configuration units or hardware configuration units such as field programmable gate array (FPGA) or application specific integrated circuit (ASIC), and execute their certain functions. 
     However, the “configuration units” are not limited to software or hardware. Each of the configuration units may be configured to be in a storage medium that can be addressed or configured to play one or more processers. 
     For example, the configuration units may include configuration units such as software configuration units, object-oriented software configuration units, class configuration units, and task configuration units, processes, functions, properties, procedures, sub-routines, segments of a program code, drivers, firmware, micro codes, circuits, data, database, data structures, tables, arrays, and variables. 
     The configuration units and functions provided in the corresponding configuration units may be combined to be a less number of configuration units or further divided into additional configuration units. 
     In this case, the optical system  211  and the optical system driving unit  212  of the data measurement unit  210  are the same in concept as the optical system  40  and the optical system driving member  50  illustrated in  FIGS. 1 and 3 . The driving control unit  213  includes the partial or whole configuration of the control module  80  illustrated in  FIGS. 1 and 3 . 
     The optical output unit  221  and the optical sensing unit  223  of the data measurement control unit  220  are the same in concept as the optical output device  60  and the optical sensing device  70  illustrated in  FIGS. 1 and 3 . The optical output control unit  222  includes the partial or whole configuration of the control module  80  illustrated in  FIGS. 1 and 3 . The data transmitting unit  224  of the data measurement control unit  220  is the same in concept as the data processing module  80  illustrated in  FIGS. 1 and 3 . 
     The data processing unit  230  illustrated in  FIG. 2  generates three-dimensional scanning model for the tooth or teeth being scanned by using data outputted from the data transmitting unit  224 . The data processing unit  230  may be included in the inside of the intra-oral scanner  100  in accordance with an illustrative embodiment or connected as a separate apparatus to the intra-oral scanner  100  through cables or the like. For restriction of a size of the intra-oral scanner  100  in accordance with an illustrative embodiment,  FIGS. 1 and 3  illustrate that the data processing unit  230  is provided outside. 
     In the intra-oral scanner  100  in accordance with an illustrative embodiment, the optical output unit  221  outputs the output light (i.e., a laser light source) toward the optical system  211  to correspond to the emission angle or the emission position set under the control of the optical output control unit  222 . Based on a value for the emission angle or the emission position controlled by the optical output control unit  222 , an A axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated. 
     In this case, the optical system  211  is in the state of being rotated based on an emission angle set in accordance with driving of the optical system driving unit  212 . Specifically, the driving control unit  213  moves the optical system  211  forwardly and backwardly in the horizontal direction depending on positions of the tooth or teeth being scanned, and rotates the optical system  211  by driving the optical system driving unit  212  in accordance with a rotation angle set in correspondence with parts to be scanned. In this case, based on a value for the rotation angle controlled by the driving control unit  213 , a B axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated. 
     Thereafter, the output light reflected through the optical system  211  is reflected from the tooth or teeth being scanned and incident again to the optical system  211 . The incident light is reflected through the optical system  211  and incident to the optical sensing unit  223 . 
     As illustrated in  FIG. 3 , the output light outputted from the optical output device  60  is reflected on the optical system  40  and projected to the tooth or teeth being scanned. The light reflected from the tooth or teeth being scanned is reflected again on the optical system  40  and incident on the optical sensing device  70 . 
     In this case, the optical sensing device  70  in accordance with an illustrative embodiment is a PSD device and generates an electrical signal depending on a position to which the incident light is inputted. That is, the optical sensing unit  223  generates position information corresponding to the generated electrical signal. The position information is a height of each of the tooth or teeth parts being scanned. In this case, a C axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated based on a value for the height sensed by the optical sensing unit  223 . 
     A PSD sensor included in the optical sensing unit  223  in accordance with an illustrative embodiment is an optical electronic sensor and has a structure, in which when an optical spot is formed on a surface, an optical current proportional to an optical energy is generated at an incidence spot and flows toward electrodes of both ends. 
     The optical sensing unit  223  in accordance with an illustrative embodiment can calculate the C axis coordinate value according to a potential measurement method using an optical triangulation method. The optical triangulation method is a potential measurement method using a two-dimensional triangulation method based on geometric optics. In the optical triangulation method, an optical system exists within one plane surface and is configured based on two optical axises being intersected with each other at an angle of θ. 
     One of the two optical axises is a condensing optical axis that forms an optical spot on a surface of an object to be measured. The other of the two optical axises is an image optical axis that transmits an image of the optical spot to the light receiving device. Here, the optical spot formed on the surface of the object to be measured is moved in a straight line on the condensing optical axis as a relative position of the object to be measured is changed. In this case, the scope of the movement refers to object trajectory. As the optical spot moves, image viscosity on the light receiving device also moves. The scope of the movement of the image spot refer to image trajectory. The image trajectory has an angle of φ to a vertical direction of the image optical axis. 
     In this case, an optical spot movement distance p on the object trajectory and an image spot movement distance q corresponding thereto can be calculated through mathematical formula 1 below. 
     
       
         
           
             
               
                 
                   p 
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                       cos 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       
                         ϕ 
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                           ( 
                           
                             s 
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                             f 
                           
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                         f 
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                         sin 
                         ⁢ 
                         
                             
                         
                         ⁢ 
                         θ 
                       
                       + 
                       
                         q 
                         ⁢ 
                         
                             
                         
                         ⁢ 
                         cos 
                         ⁢ 
                         
                             
                         
                         ⁢ 
                         ϕ 
                         ⁢ 
                         
                             
                         
                         ⁢ 
                         cos 
                         ⁢ 
                         
                             
                         
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                         θ 
                       
                     
                   
                 
               
               
                 
                   [ 
                   
                     Mathematical 
                     ⁢ 
                     
                         
                     
                     ⁢ 
                     Formula 
                     ⁢ 
                     
                         
                     
                     ⁢ 
                     1 
                   
                   ] 
                 
               
             
           
         
       
     
     f is a focal length of an image lens to project an image in accordance with the optical spot to the light receiving device. s is a distance between the image lens and an actual object to be measured. 
     The angle of φ can be calculated through mathematical formula 2 below.
 
 =tan −1 ( f /( s−f )tan θ)  [Mathematical Formula 2]
 
     If the optical triangulation is applied to an illustrative embodiment, the output light forms an optical spot on the surface of the tooth or teeth being scanned. The light reflected on the tooth or teeth being scanned (i.e., incident light) forms an image on the PSD sensor again. Then, the PSD sensor outputs an electrical signal depending on the image forming position of the incident light. In this case, since the position where an image is formed on the PSD sensor varies depending on variation of the heights of the teeth, values for the heights of the tooth or teeth can be measured. 
     Subsequently, the data transmitting unit  224  matches the A and B axis coordinate values acquired through the optical output control unit  222  and the driving control unit  213  with the C axis coordinate value acquired from the light sensing unit  223  and transmits the values to the data processing unit  230 . 
     For example, the data transmitting unit  224  calculates the A coordinate value depending on the emission angle or the emission position of the light from the optical output unit  221  controlled by the optical output control unit  222 . The data transmitting unit  224  calculates the B coordinate value depending on the emission angle of the optical system  211  controlled by the driving control unit  213 . The data transmitting unit  224  calculates the C coordinate value depending on the position of the light incident to the optical sensing unit  223 . 
     The data processing unit  230  generates three-dimensional scanning model for the tooth or teeth being scanned based on input three-dimensional data information. 
     Specifically, the three-dimensional data generating unit  231  of the data processing unit  230  generates the three-dimensional scanning model for the tooth or teeth being scanned by combining the A, B, and C axis coordinate values received from the data transmitting unit  224  and associated with one another. 
     The data storage  232  sequentially stores the generated three-dimensional scanning model for the tooth or teeth being scanned in a database or others. 
     In this case, the intra-oral scanner  100  in accordance with an illustrative embodiment can output the three-dimensional scanning model for the patient&#39;s teeth stored in the data storage  232  through a screen provided therein (not illustrated), an output system (not illustrated) connected through data cables, or others. 
       FIG. 4  is a plane view of an intra-oral scanner in accordance with another illustrative embodiment.  FIG. 5  is a block diagram showing configuration of an intra-oral scanner in accordance with another illustrative embodiment.  FIG. 6  is a side view of an intra-oral scanner in accordance with another illustrative embodiment. 
     Unlike the intra-oral scanner  100 , the intra-oral scanner  100 ′ in accordance with another illustrative embodiment provides a method of secondarily reflecting the output light to be projected to the tooth or teeth being scanned. For simplification of descriptions,  FIGS. 4 to 6  omit detailed descriptions of the configuration units of the intra-oral scanner  100 ′, which are the same as those of the intra-oral scanner  100 . 
     Specifically, as illustrated in  FIGS. 4 to 6 , the intra-oral scanner  100 ′ in accordance with another illustrative embodiment includes a guide  403 , a second optical system  404 , and a second optical system driving unit  405  in the inside of an insertion unit  401 . The intra-oral scanner  100 ′ includes an optical output device  406 , a first optical system  407 , a first optical system driving member  408 , an optical sensing device  409 , a control module  410 , and a data processing module  411  in the inside of a body  402 . 
     In this case, the intra-oral scanner  100 ′ in accordance with another illustrative embodiment primarily reflects the output light outputted from the optical output device  406  through the first optical system  407  and outputs the light to the second optical system  404 . In this case, the first optical system driving member  408  rotates the first optical system  407  along the second reference axis so as to change an emission angle of the output light. The first optical system driving member  408  moves the first optical system  407  in left and right directions in a sling manner so as to change an emission position of the output light. 
     Hereinafter, a teeth modeling method through three-dimensional scanning in the intra-oral scanner  100 ′ in accordance with another illustrative embodiment will be described with reference to  FIG. 5 . 
     With respect to the configuration of the intra-oral scanner  100 ′ in accordance with another embodiment in  FIGS. 4 and 6 ,  FIG. 5  illustrates a block diagram for a data measurement unit  510 , a data measurement control unit  520 , and a data processing unit  530  based on data to be processed. 
     The configuration units in accordance with another illustrative embodiment in  FIG. 5  mean software configuration units or hardware configuration units such as field programmable gate array (FPGA) or application specific integrated circuit (ASIC), and execute their certain functions. However, the “configuration units” are not limited to software or hardware. Each of the configuration units may be configured to be in a storage medium that can be addressed or configured to play one or more processers. 
     For example, the configuration units may include configuration units such as software configuration units, object-oriented software configuration units, class configuration units, and task configuration units, processes, functions, properties, procedures, sub-routines, segments of a program code, drivers, firmware, micro codes, circuits, data, database, data structures, tables, arrays, and variables. 
     The configuration units and functions provided in the corresponding configuration units may be combined to be a less number of configuration units or further divided into additional configuration units. 
     The second optical system  511  and the second optical system driving unit  512  of the data measurement unit  510  are the same in concept as the second optical system  404  and the second optical driving member  405  illustrated in  FIGS. 4 and 6 . The second driving control unit  513  includes the partial or whole configuration of the control module  410  illustrated in  FIGS. 4 and 6 . 
     The second optical system  511 , the second optical system driving unit  512 , and the second driving control unit  513  execute the same operations as those of the optical system  211 , the optical system driving unit  212 , and the driving control unit  213  in accordance with an illustrative embodiment in  FIG. 2 . 
     The first optical system  521  and the first optical system driving unit  522  of the data measurement control unit  520  are the same in concept as the first optical system  407 , and the first optical system driving member  408  illustrated in  FIGS. 4 and 6 . The first driving control unit  523  includes the partial or whole configuration of the control module  410 . 
     The optical output unit  524  and the optical sensing unit  525  of the data measurement control unit  520  are the same in concept as the optical output device  406  and the optical sensing device  409  illustrated in  FIGS. 4 and 6 . The data transmitting unit  526  includes the partial or whole configuration of the data processing module  411  illustrated in  FIGS. 4 and 6 . 
     Meanwhile, in  FIG. 5 , the data processing unit  530  generates three-dimensional scanning model for the tooth or teeth being scanned by using data outputted from the data transmitting unit  526 . The data processing unit  530  may be included in the intra-oral scanner  100 ′ in accordance with another illustrative embodiment or connected as a separate apparatus to the intra-oral scanner  100 ′ through cables or others. For restriction of a size of the intra-oral scanner  100 ′ in accordance with another illustrative embodiment,  FIGS. 4 and 6  illustrates that the data processing unit  530  is provided outside. 
     The optical sensing unit  525 , the data transmitting unit  526 , and the data processing unit  530  execute the same operations as those of the optical sensing unit  223 , the data transmitting unit  224 , and the data processing unit  230  in accordance with an illustrative embodiment in  FIG. 2 . 
     First, in the intra-oral scanner  100 ′ in accordance with another illustrative embodiment, an output light (i.e., a laser light) outputted from the optical output unit  524  in a straight line is primarily reflected at the emission angle or the emission position set through the first optical system  521 . 
     Specifically, the first optical system  521  is in the state of being rotated at the set emission angle as the first optical driving unit  522  is driven under control by the first driving control unit  523 . Here, the first optical system driving unit  522  rotates the first optical system  521  along the second reference axis under a command from the first driving control unit  523  so as to changes the emission angle of the output light. The second reference axis is consistent with the C axis illustrated in  FIG. 4 . In this case, the A axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated based on a value for the emission angle controlled by the first driving control unit  523 . 
     In another illustrative embodiment, the first optical driving system driving unit  522  may move the first optical system  521  in left and right directions in a sliding manner so as to change the emission position of the output light. In this case, the A axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated based on a value for the emission position controlled by the first driving control unit  523 . 
     The output light reflected through the first optical system  521  is projected to the second optical system  511 . The output light is secondarily reflected from the second optical system  511  at the set emission angle and projected to the tooth or teeth being scanned. In this case, the second optical system  511  is in the state of being rotated at the set emission angle as the second optical system driving unit  512  is driven under control by the second driving control unit  513 . The second optical system  511  is rotated along the first reference axis. The first reference axis is consistent with the A axis illustrated in  FIG. 4 . In this case, the B axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated based on a value for the emission angle controlled by the second driving control unit  513 . 
     Thereafter, the output light reflected through the second optical system  511  is reflected from the tooth or teeth being scanned and incident again to the second optical system  511 . The incident light is reflected through the second optical system  511  and incident to the optical sensing unit  525 . 
     That is, as illustrated in  FIG. 6 , the output light outputted from the optical output device  406  is primarily reflected on the first optical system  407  and projected to the second optical system  404 . The output light secondarily reflected on the second optical system  404  is projected to the tooth or teeth being scanned. The incident light reflected from the tooth or teeth being scanned is reflected again on the second optical system and incident to the optical sensing device  409 . 
     Accordingly, the optical sensing unit  525  generates position information corresponding to an electrical signal depending on a position to which the incident light is incident. The position information is a height of each of the tooth or teeth parts being scanned. Based on values of the heights sensed by the optical sensing unit  525 , the C axis coordinate value for the output light projected to the tooth or teeth being scanned can be calculated. 
     Thereafter, the data transmitting unit  526  matches the A and B axis coordinate values acquired through the first driving control unit  523  and the second driving control unit  513  with the C axis coordinate value acquired from the optical sensing unit  523  and transmits the values to the data processing unit  530 . 
     The data processing unit  530  generates three-dimensional scanning model for the tooth or teeth being scanned based on the input three-dimensional data information. 
     Specifically, the three-dimensional data generating unit  531  of the data processing unit  530  generates the three-dimensional scanning model for the tooth or teeth being scanned by combining the A, B, C axis coordinate values received from the data transmitting unit  526  and associated with one another. 
     The data storage  532  sequentially stores the generated three-dimensional scanning model for the tooth or teeth being scanned in a database or others. 
     The apparatus and the system of the illustrative embodiment have been described in relation to the certain examples. However, the components or parts or all the operations of the apparatus and the system may be embodied using a computer system having universally used hardware architecture. The above description of the illustrative embodiments is provided for the purpose of illustration, and it would be understood by those skilled in the art that various changes and modifications may be made without changing technical conception and essential features of the illustrative embodiments. Thus, it is clear that the above-described illustrative embodiments are illustrative in all aspects and do not limit the present disclosure. For example, each component described to be of a single type can be implemented in a distributed manner. Likewise, components described to be distributed can be implemented in a combined manner. 
     The scope of the inventive concept is defined by the following claims and their equivalents rather than by the detailed description of the illustrative embodiments. It shall be understood that all modifications and embodiments conceived from the meaning and scope of the claims and their equivalents are included in the scope of the inventive concept.