Dental optical measuring device and dental optical measuring / diagnostic tool

Abstract

A dental optical measuring device with: an optical three-dimensional surface measurement system structure with a measurement result display area for displaying at least one measurement result, a measurement control range for controlling a measurement, a measurement light emission area for emitting measurement light, a scanning mirror suitable for scanning with the measuring light, an outward-leading opening through which the measuring light is directed onto a target of the measurement, a light transmission path to guide the measuring light to the outgoing opening, an incoming aperture onto which the measuring light directed from the outgoing aperture falls, after it has been scattered at the target of the measurement, a light reception path to guide the scattered light incident on the incoming opening and a light reception area for receiving the scattered light guided through the light reception path; and an optical coherence tomography measurement system structure with a measurement result display area for displaying at least one measurement result, a measurement control range for controlling a measurement, a measurement light emission area for emitting measurement light, a light splitting area for dividing the measurement light into measurement light and reference light, a scanning mirror suitable for scanning with the measuring light, an outward-leading opening through which the measuring light is directed onto the target of the measurement, a light transmission path to guide the measuring light to the outgoing opening, an incoming aperture onto which the measurement light directed from the outgoing aperture falls, after it has been scattered at the target of the measurement, a light reception path to guide the scattered light incident on the incoming opening, a reflective mirror for reflecting the reference light obtained as a result of the division carried out by the light splitting area, a light interference area to generate interference between the light reflected by the reflecting mirror and the scattered light and a receiving area for coherent light for receiving coherent light generated by the interference performed by the light interference area; wherein: The light transmission path and the light reception path have a lens system light guide path for guiding the measurement light to the outgoing aperture and for guiding the scattered light from the incoming aperture; The light transmission path and the light reception path of the optical coherence tomography measurement system structure are located on an optical axis of the lens system light guide path; the light transmission path and the light reception path of the optical three-dimensional surface measurement system structure are located at an eccentric point that is eccentric from the optical axis of the lens system light guide path; the optical three-dimensional surface measurement system structure and the optical coherence tomography measurement system structure share at least one of the measurement result display area, the measurement control area, the measurement light emission area, the scanning mirror, the light transmission path, the outgoing aperture, the incoming aperture and the light reception path; at least the scanning mirror, the light transmission path, the outgoing aperture, the incoming aperture and the light reception path must be shown in a diagnostic tool suitable for making a diagnosis about the target of the measurement.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention:

[0001] The present invention relates to a dental optical measuring device and a dental optical measuring / diagnostic tool suitable, for example, for making a diagnosis in an oral cavity. 2. Description of the state of the art:

[0002] Along with the advancement of diagnostic techniques, it is more desirable than ever to obtain detailed and accurate information about the location of a diagnostic item.

[0003] For example, Patent Literature 1 proposes a dental tomographic image display system that obtains a tomographic image of a tooth and gum by using optical coherence tomography.

[0004] The dental tomography image display system described in Patent Document 1 scans a specific area with light of an oscillation wavelength, allows the light to be incident on a probe, performs scanning and illumination with display light using an optical coherence meter and a scanning optical path changing section provided in the probe, and causes interference between a light scattered by a detection object and a reference light in the probe to obtain coherent light. The dental tomography image display system is configured to process the coherence signal using Fourier transformation to obtain an image signal in a depth direction, and further to localize the image based on a scanning direction to obtain two-dimensional tomography images from the optical coherence tomography information.

[0005] As another method, Patent Document 2 proposes a dental three-dimensional camera for capturing a surface structure of a location of a diagnostic object by triangulation.

[0006] The optical coherence tomography information obtained by the tomographic image display system disclosed in Patent Document 1 and the three-dimensional shape information obtained by the three-dimensional camera disclosed in Patent Document 2 differ from each other. Therefore, a suitable device must be used among the diagnostic devices used for each method to obtain information suitable for a specific part of the location of the diagnosis object or the content of the diagnosis.

[0007] However, these diagnostic devices are independent of each other. Obtaining optical coherence tomography information and three-dimensional shape information requires large-scale facilities. Furthermore, it is necessary to first obtain information about the location of the diagnostic object using either an optical coherence tomography information acquisition device, such as a tomographic image display system, or a three-dimensional shape information acquisition device, such as a three-dimensional camera, and then interchange the devices to obtain the other information.

[0008] Amaechi, B. [et al]: Application of Optical Coherence Tomography for imaging and assessment of early dental caries lesions. Laser Physics. 13, 2003, pp. 703 to 710 deals with the combined use of optical coherence tomography and confocal imaging techniques.

[0009] DE 10 2009 001 086 A1 describes a handheld dental camera for optical 3D measurement.

[0010] Rominu M. [et al]: Adhesive Improvement in Optical Coherence Tomography Combined with Confocal Microscopy for Class V Cavities Investigations. Proc. of SPIE, Vol. 7626, 2010, pp. 76260Y-1 to 76260Y-8 describes the combined use of optical coherence tomography and confocal imaging techniques.

[0011] US 2010 / 0 296 098 A1 describes a handheld measuring device for optical coherence tomography. [List of prior art literature][Patent specifications] Patent Document 1: Japanese Patent Laid-Open Publication JP 2008- 58 138 A Patent Document 2: Japanese National Phase Disclosed PCT Patent Publication JP 2006 - 525 066 A SUMMARY OF THE INVENTION [Problems Solved by the Invention]

[0012] In light of the problems described above, the present invention aims to provide a dental optical measuring device and a dental optical measuring / diagnostic tool capable of acquiring both optical coherence tomography information and three-dimensional shape information, having a compact structure, and eliminating the need for device replacement. [Solution to the problems}

[0013] This objective is achieved by the subject matter of the claims.

[0014] The claimed three-dimensional optical surface measuring system structure may further be configured as a device for measuring the shape of the location of the diagnosis object in a non-contact manner, for example, by a triangulation method such as a light spot projection method (fiber optic method), a light cutout method (light slit projection method), a light pattern projection method (spatial coding method), a phase shift method or the like, a confocal method, a focal point method or the like.

[0015] The claimed optical coherence tomography measuring system structure may further be formed, for example, from an OCT (optical coherence tomography) device, a TD-OCT (time domain OCT), SD-OCT (spectral domain OCT), SS-OCT (swept source OCT), or the like.

[0016] The diagnostic tool is called a “handheld device” and performs, for example, the taking of impressions by inserting a part of it into the oral cavity.

[0017] According to the invention defined by the subject matter of the claims, an apparatus for acquiring both optical coherence tomography information and three-dimensional shape information can be provided, which has a compact structure and makes exchange of apparatus unnecessary.

[0018] This will be described in more detail. At least one of the measurement result display section, the measurement control section, the measurement light-emitting section, the scanning mirror, the light transmission path, the outgoing port, the incoming port, and the light receiving path is shared between the three-dimensional optical surface measurement system structure and the optical coherence tomography measurement system structure. Due to this, the dental optical measurement device can be more compact compared to the case where an optical coherence tomography information acquisition device and a three-dimensional shape information acquisition device are provided separately.

[0019] Additionally, the diagnostic tool includes at least one of the scanning mirror, the light transmission path, the outgoing aperture, the incoming aperture, and the light reception path, suitable for making a diagnosis about the measurement target. Therefore, both optical coherence tomography information and three-dimensional shape information can be obtained by one diagnostic tool without requiring device replacement.

[0020] Therefore, a dental optical measuring device can obtain both information about the interior of the diagnostic object based on optical coherence tomography information and surface information about the diagnostic object based on information about the three-dimensional surface shape. These pieces of information are synthetic and complementary to each other. As a result, high-precision three-dimensional spatial data can be obtained, including the tomography of the interior of the oral cavity. The high-precision three-dimensional spatial data is suitable as impression data for producing a prosthetic application for dental treatment and is further suitable for high-precision diagnosis of incipient dental caries on the surface or inside the tooth, root fractures, and the like.The high-precision three-dimensional spatial data is also suitable as data for planning the embedding of implants.

[0021] The light transmission path and the light reception path include a lens system light guide path for guiding the measurement light to the outgoing opening and for guiding the scattered light out of the incoming opening.

[0022] Therefore, the optical paths can be guided more stably compared to an optical path formed from a light guide or similar material. The refractive index, light transmission ratio, and the like of the lens can be adjusted to provide a predetermined level of performance.

[0023] The light transmission path and the light reception path of the optical coherence tomography measurement system structure are located on an optical axis of the lens system light guide path, and the light transmission path and the light reception path of the three-dimensional surface measurement system structure are located at an eccentric position that is eccentric with respect to the optical axis of the lens system light guide path.

[0024] Therefore, the light transmission path and the light reception path of the optical three-dimensional surface measurement system structure for performing measurement by triangulation and the light transmission path and the light reception path of the optical coherence tomography measurement system structure can be constructed while maintaining the precision of both without mutual interference in the same lens system light guide path.

[0025] In one embodiment of the invention, the three-dimensional surface optical measurement system structure and the optical coherence tomography measurement system structure may share the scanning mirror, the light transmission path, the outgoing opening, the incoming opening, and the light receiving path.

[0026] According to this invention, the three-dimensional optical surface measurement system structure and the optical coherence tomography measurement system structure share a plurality of elements. Therefore, the dental optical measurement device can be more compact.

[0027] In one embodiment of the invention, the measurement light emission region of the three-dimensional surface optical measurement system structure and the measurement light emission region of the coherence tomography optical measurement system structure may be provided individually.

[0028] According to this invention, the measurement light suitable for each type of measurement can be emitted for the measurement. Since the measurement light emission region of the optical three-dimensional surface measurement system structure and the measurement light emission region of the optical coherence tomography measurement system structure are provided separately, the measurement light can be emitted from the measurement light emission regions at the same time. Therefore, the optical coherence tomography information and the three-dimensional shape information can be obtained simultaneously.

[0029] In one embodiment of the invention, the light splitting portion and the light interference portion may be provided as a light splitting / interference portion for splitting the measurement light into the measurement light and the reference light and causing interference of the reflected reference light and the scattered light to generate coherent light in one piece.

[0030] The light splitting / interference region can be formed from a component called a “2 x 2 fiber coupler.”

[0031] According to this invention, the dental optical measuring device having the light splitting / interference portion can be more compact as compared with the case where the light splitting portion for splitting the measurement light into the measurement light and the reference light and the light interference portion for causing interference of the reflected reference light and the scattered light to generate coherent light are provided individually.

[0032] In one embodiment of the invention, the scanning mirror, the light splitting / interference region, the light transmission path, the outgoing opening, the light receiving path, the reflecting mirror, the coherent light receiving region, and the incoming opening of the optical coherence tomography measurement system structure may be included in the diagnostic tool.

[0033] According to this invention, the measurement light is split by the light splitting / interference region and directed to the location of the diagnostic object via the light transmission path and the outgoing aperture. The measurement light is also reflected by the reflecting mirror. The scattered light incident on the incoming aperture after being scattered at the location of the diagnostic object and the reference light reflected by the reflecting mirror are used to generate coherent light by the light splitting / interference region, and the coherent light is received by the coherent light receiving region. In this way, the optical coherence tomography information can be obtained. [Effect of the invention]

[0034] According to the present invention, a dental optical measuring device and a dental optical measuring / diagnostic tool can be provided which are capable of acquiring both optical coherence tomography information and three-dimensional shape information, which have a compact structure and which make device replacement unnecessary. BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a schematic structural view of a dental optical measuring device. Fig. Figure 2 is a schematic cross-sectional view of a handset. Fig. Figure 3 shows a schematic diagram of a light transmission / reception path. Fig. 4 is a schematic structural view of an OCT measuring device. Fig. 5 schematically shows a structure of a surface shape measuring device. Fig. 6 shows schematic structures of dental optical measuring devices of other embodiments. Fig. 7 is a schematic structural view of a dental optical measuring device of another embodiment. DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0035] An embodiment of the present invention will be described below with reference to the drawings. Fig. 1 is a schematic structural view of a dental optical measuring device 1. Fig. 2 is a schematic cross-sectional view of a handset 10. Fig. 3 schematically shows a light transmission / reception path 40 of the handset 10. Fig. 4 is a schematic structural view of an OCT measuring device A. Fig. 5 schematically shows a structure of a surface shape measuring device B.

[0036] The dental optical measuring device 1 is a diagnostic device suitable for obtaining high-precision three-dimensional spatial data, which includes a tomography of the interior of the location of the diagnostic object 100 and is suitable, for example, for taking impressions. As shown, for example, in the enlarged part “a” of the Fig. 1, taking an impression of a marginal area 103, the cervix dentis 101 at the location of the diagnostic object 100 and covered with gums 102, cannot be performed excluding the gums 102. It goes without saying that both a part of the tooth 101 not covered by the gums 102 and the marginal area 103 can be determined as the location of the diagnostic object 100, and that precise three-dimensional spatial data can be obtained therefrom.

[0037] To obtain such data, the dental optical measuring device 1 comprises an OCT measuring device A for obtaining information about the inside of the location of the diagnostic object 100 by OCT, and a surface shape measuring device B for obtaining information about the three-dimensional shape of a surface of the location of the diagnostic object 100 by a surface measuring method such as triangulation or the like.

[0038] This is described in more detail. As in Fig. As shown in Figure 4, the OCT measurement device A for obtaining information about the interior of the location of the diagnostic object 100 by OCT includes a control device 3a connected to a display device 2a formed of an output screen, a light source 20a for emitting OCT measurement light LbA, and a light splitting / interference portion 70. The light splitting / interference portion 70 splits the OCT measurement light LbA emitted from the light source 20a into reference light LbA1 and illumination measurement light LbA2, and causes interference of the scattered light SbA obtained as a result of the backscattered illumination measurement light LbA2 directed toward the location of the diagnostic object 100 and the reflected light RbA described later to obtain coherent light Kb. The light splitting / interference region 70 is formed, for example, from a 2 x 2 fiber coupler.The OCT measuring device A further includes a scanning mirror 30a for aligning the illumination measurement light LbA2 such that objective lenses 40L located in an OCT light transmission / reception part 40a are scanned with the illumination measurement light LbA2, a reflecting mirror 72 for reflecting the reference light LbA1 obtained as a result of division performed by the light splitting / interference section 70 as reflected light RbA, a light transmission / reception path 71 for guiding the reference light LbA1 and the reflected light RbA between the light splitting / interference section 70 and the reflecting mirror 72, and a light receiving device 60a for converting the coherent light Kb obtained as a result of interference performed by the light splitting / interference section 70 into an electrical signal. The light receiving device 60a is formed of a photodiode or the like.

[0039] The OCT measurement device A structured as described above operates as follows. The OCT measurement light LbA directed by the light source 20a is split into the illumination measurement light LbA2 and the reference light LbA1 by the light splitting / interference section 70. The illumination measurement light LbA2 is reflected at the location of the diagnosis object 100 to become the scattered light SbA, and the reference light LbA1 is reflected by the reflecting mirror 72 to become the reflected light RbA. The light splitting / interference section 70 receives the scattered light SbA and the reflected light RbA to obtain the coherent light Kb.

[0040] The control device 3a detects the intensity of the coherent light Kb obtained by the interference of the reflected light RbA and the scattered light SbA and thus obtains optical coherence tomography information of the location of the diagnostic object 100.

[0041] This operation is performed for each of the various parts of the location of the diagnostic object 100 that is a target of information acquisition, while the location of the diagnostic object 100 is scanned with light by the scanning mirror 30a in such a way that the part thereof illuminated with light is varied. In this way, optical coherence tomography information about each part is obtained. In this way, optical coherence tomography information with a substance profile at a certain depth below the surface of the location of the diagnostic object 100 is obtained. For example, an image of the surface shape of the tooth 101 or gum 102 and also a substance profile of the interior of the tooth 101 or gum 102 are obtained. In particular, when the cervix dentis, also called the marginal area, is covered with gum 102, substance information of the cervix dentis of the tooth 101 is obtained.This optical coherence tomography information is subjected to image processing and thus information about the interior location of the diagnostic object 100 is obtained.

[0042] The surface shape measuring device B acquires the information about the three-dimensional shape of the surface of the location of the diagnostic object 100 by a surface measuring method such as triangulation or the like and converts the information about the three-dimensional shape into an image. As shown in Fig. As shown in Figure 5, the surface shape measuring device B includes a control device 3b connected to a display device 2b formed of an output screen, a light source 20b for emitting surface measurement light LbB, a scanning mirror 30b for directing the surface measurement light LbB emitted by the light source 20b so that the objective lenses 40L located in a surface measurement light transmitting / receiving part 40b are scanned with the surface measurement light LbB, and a light receiving device 60b for receiving the scattered light SbB obtained as a result of the surface measurement light LB directed toward the location of the diagnosis object 100 and scattered back from the surface of the location of the diagnosis object, and for converting the scattered light SbB into an electrical signal. The light receiving device 60b is formed of a CCD camera or the like.

[0043] The surface shape measuring device B structured as described above operates as follows. Fig. Figure 5(a) shows a state in which the surface measurement light LbB is aligned by triangulation. As in Fig. As shown in Fig. 5(a), the location of the diagnostic object 100 is scanned while being illuminated with the surface measurement light LbB. The light receiving device 60b receives the scattered light SbB obtained as a result of the backscattered surface measurement light LB directed onto the location of the diagnostic object 100 in an oblique direction (see Fig. 5(b)) and can thus measure the surface shape of the location of the diagnostic object 100 and generate an image thereof (see Fig. 5(c)).

[0044] The dental optical measuring device 1 includes the OCT measuring device A, which is suitable for obtaining information about the interior of the location of the diagnostic object 100, and the surface shape measuring device B, which is suitable for obtaining information about the three-dimensional shape of the surface of the location of the diagnostic object 100. Therefore, the dental optical measuring device 1 includes the display device 2, the control device 3, the light sources 20, the scanning mirror 30, the light transmission / reception path 40, an inlet / outlet opening 50, the light receiving device 60, the light splitting / interference region 70, the light transmission / reception path 71, and the reflecting mirror 72. The scanning mirror 30, the light transmission / reception path 40, and the inlet / outlet opening 50 are provided by the handheld device 10.

[0045] This will be described in more detail. The display device 2 is connected to the control device 3 described later and is controlled by the control device 3 to display an operation menu for and measurement results from the dental optical measuring device 1. The display device 2 also receives operating inputs.

[0046] The control device 3 is connected to the display device 2, the light source 20 (described later), the scanning mirror 30, and the light receiving device 60, and controls these elements. The control device 3 includes a memory area, a CPU, and the like.

[0047] The light sources (20a, 20b) are controlled by the control section 3 to emit laser light suitable for the respective type of measurement.

[0048] The scanning mirror 30 reflects light directed at it and changes the direction in which the light is guided. The scanning mirror 30 is controlled by the control device 3 to adjust its orientation.

[0049] The light transmission / reception path 40 has the objective lenses 40L suitable for guiding light, arranged in a longitudinal direction of the handset 10.

[0050] The inlet / outlet opening 50 allows light to enter or exit the dental optical measuring device 1.

[0051] In the dental optical measuring device 1, the display device 2, the control device 3, the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50 act as the respective elements of the OCT measuring device A and the surface shape measuring device B. In other words, in the dental optical measuring device 1, the display device 2, the control device 3, the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening are shared by the OCT measuring device A and the surface shape measuring device B.

[0052] However, as described in more detail later, the light transmission / reception path 40 shared by the OCT measuring device A and the surface shape measuring device B includes an OCT light transmission / reception part 40a and a surface measurement light transmission / reception part 40b, which differ from each other in their light entrance parts. The incoming / outgoing opening 50 shared by the OCT measuring device A and the surface shape measuring device B includes an OCT incoming / outgoing opening 50a and a surface measurement incoming / outgoing opening 50b, which differ from each other in their light entrance parts.

[0053] The light source 20 includes the light sources 20a and 20b, which are not shared by the OCT measuring device A and the surface shape measuring device B, and the light receiving device 60 includes the light receiving devices 60a and 60b, which are not shared by the OCT measuring device A and the surface shape measuring device B. The light splitting / interference region 70, the light transmission / reception path 71, and the reflecting mirror 72 are included only in the OCT measuring device A.

[0054] The length of an optical path from the light splitting / interference portion 70 to the reflecting mirror 72 to which the reference light LbA1 is guided is set equal to the length of the optical path from the light splitting / interference portion 70 via the scanning mirror 30, the light transmitting / receiving path 40, and the incoming / outgoing opening 50 to the location of the diagnosis object 100 to which the illumination measurement light LbA2 is guided.

[0055] In the dental optical measuring device 1 structured as described above, as shown in Fig. 2, the handheld device 10, which includes the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50, is a diagnostic tool that is generally cylindrical in shape. The handheld device 10 receives outgoing light Lb (LbA, LbB) directed to a rear end 10a (left in Fig. 2) of it, and directs the light Lb from a pointed end 10b (right in Fig. 2) which can be inserted into the oral cavity, downwards.

[0056] This will be described in more detail. The handheld device 10 includes entrance regions 11 (11a, 11b) located at the rear end 10a, a first mirror 12a, a beam combiner 12b, second mirrors 12c, the scanning mirror 30, a beam splitter 12d, the light transmission / reception path 40, a third mirror 12e, the inlet / outlet aperture 50, a fourth mirror 12f, the light receiving device 60b, and a lens 13. The entrance regions 11 (11a, 11b) respectively introduce the illumination measurement light LbA2 obtained as a result of the OCT measurement light LbA from the light source 20a in the OCT measuring device A being split by the light splitting / interference region 70, and the surface measurement light LbB from the light source 20b in the surface shape measuring device B. The first mirror 12a changes the guiding direction of the surface measurement light LbB introduced from the entrance region 11b.The beam combiner 12b changes the guiding direction of the illumination measurement light LbA2 introduced from the entrance portion 11a and allows the surface measurement light LbB, whose guiding direction has been changed by the first mirror 12a, to pass through it. The second mirrors 12c change the guiding direction of the outgoing light Lb (LbA2, LbB) so that the outgoing light Lb does not pass through the scanning mirror 30 described later. The scanning mirror 30 adjusts the guiding direction of the outgoing light Lb. The beam splitter 12d allows the outgoing light LB, whose guiding direction has been changed by the adjustment performed by the scanning mirror 30, to pass through it, allows the scattered light SbA described later to pass through it, and changes the guiding direction of the scattered light SbB. The light transmission / reception path 40 allows the outgoing light Lb and the scattered light Sb to be passed through it.The third mirror 12e changes the direction of the outgoing light Lb that has passed through the light transmission / reception path 40 so that the outgoing light is directed toward the incoming / outgoing opening 50, and changes the direction of the scattered light Sb incident on the incoming / outgoing opening so that the scattered light Sb is directed toward the light transmission / reception path 40. The incoming / outgoing opening 50 directs the outgoing light Lb toward the location of the diagnostic object 100 and allows the light Sb backscattered by the location of the diagnostic object 100 to enter the handset.The fourth mirror 12f changes the guiding direction of the scattered light SbB that has passed through the light transmission / reception path 40 from the tip end 10b to the rear end 10a and whose guiding direction has been changed by the beam splitter 12d, so that the scattered light SbB is directed to the light receiving device 60b described later. The receiving device 60b receives the scattered light SbB that has passed through the fourth mirror 12f and is formed of a CMOS device or the like. The lens 13 is located between the fourth mirror 12f and the light receiving device 60b.

[0057] The scanning mirror 30 and the light receiving device 60b, which are provided by the handset 10, are connected to the control device 3 ( Fig. 1) and are controlled by them.

[0058] As in Fig. As shown in Figure 3(a), the illumination measurement light LbA2 and the scattered light SbA pass through the center of the objective lenses 40L included in the light transmission / reception path 40 or its vicinity, and the surface measurement light LbB and the scattered light SbB pass through positions of the objective lenses 40L that are eccentric from the center. A region including the center of the objective lenses 40 and its vicinity, through which the illumination measurement light LbA2 and the scattered light SbA pass, is referred to as the OCT light transmission / reception part 40a, and the position eccentric from the center of the objective lenses 40L through which the surface measurement light LbB and the scattered light SbB pass is referred to as the surface measurement light transmission / reception part 40b (40b1, 40b2).

[0059] According to an OCT measurement technique, the illumination measurement light LbA2 exiting from the OCT inlet / outlet port 50a and the scattered light SbA incident from the location of the diagnostic object 100 onto the OCT inlet / outlet port 50a must travel along the same optical path. According to a triangulation technique, the surface measurement light LbB exiting from the surface measurement inlet / outlet port 50b and the scattered light SbB incident from the location of the diagnostic object 100 onto the surface measurement inlet / outlet port 50b must travel along optical paths having a triangulation angle of 2θ with respect to each other. θ is an angle formed by an optical axis of the objective lenses 40L and the optical path of the surface measurement light LbB emerging from the objective lenses 40L.If the amount of eccentricity of the surface measurement light LbB with respect to the optical axis of the objective lenses 40L is denoted by s and the focal length of the objective lenses 40L is denoted by f, tanθ = s / f.

[0060] A fiber optic path in a handset 10 structured as described above is described.

[0061] The illumination measurement light LbA2 obtained as a result of the OCT measurement light LbA emitted by the light source 20a being split by the light splitting / interference region 70 is introduced into the handset 10 through the entrance region 11a. Similarly, the surface measurement light LbB emitted by the light source 20b is introduced into the handset 10 through the entrance region 11b.

[0062] The guiding direction of the surface measurement light LbB introduced from the entrance region 11b is changed by the first mirror 12a. The surface measurement light LbB then passes through the beam combiner 12b. The guiding direction of the illumination measurement light LbA2 introduced from the entrance region 11a is changed by the beam combiner 12b. The illumination measurement light LbA2 and the surface measurement light LbB, which has passed through the beam combiner 12b, have their guiding directions changed by the second mirrors 12c to bypass the scanning mirror 30 and are guided onto the scanning mirror 30.

[0063] The outgoing light Lb (LbA2, LbB), whose guiding direction is changed by the scanning mirror 30 controlled by the control device 3, passes through the beam splitter 12d and then through the light transmission / reception path 40. In this case, the illumination measurement light LbA2 passes through the OCT light transmission / reception part 40a of the light transmission / reception path 40, and the surface measurement light LbB passes through the surface measurement light transmission part 40b1 of the light transmission / reception path 40.

[0064] The outgoing light Lb, which has passed through the light transmission / reception path 40 and whose guiding direction is changed by the third mirror 12e, exits the incoming / outgoing opening 50 toward the location of the diagnostic object. The outgoing light Lb, which has exited the incoming / outgoing opening 50, is scattered backward by a surface and the interior of the location of the diagnostic object. The scattered light Sb (SbA, SbB) enters the handset 10 through the incoming / outgoing opening 50. The scattered light Lb, which had been incident on the incoming / outgoing opening 50 and whose guiding direction is changed by the third mirror 12e to be directed toward the light transmission / reception path 40, passes through the light transmission / reception path 40 from the tip end 10b.In this case, the scattered light SbA passes through the OCT light transmission / reception part 40a of the light transmission / reception path 40, and the scattered light SbB passes through the surface measurement light reception part 40b2 of the light transmission / reception path 40.

[0065] The scattered light SbB, which has passed through the surface measurement light receiving part 40b2 of the light transmission / reception path 40 and whose guiding direction is changed by the beam splitter 12d and the fourth mirror 12f, passes through the lens 13 to be directed onto the light receiving device 60b. The light receiving device 60b, having received the scattered light SbB directed thereto, transmits the image information to the control device 3 as an electrical signal.

[0066] The scattered light SbA that has passed through the OCT light transmission / reception part 40a of the light transmission / reception path 40 passes through the beam splitter 12d. The guiding direction of the scattered light SbA is changed by the scanning mirror 30 and is combined by the second mirrors 12c and the beam combiner 12b to be guided out of the handset 10 through the entrance area 11a.

[0067] While the orientation of the scanning mirror 30 is controlled by the control device 3 to be changed such that the outgoing light Lb passes through the optical path as described above, the surface of the location of the diagnosis object 100 is scanned with the outgoing light Lb for measurement.

[0068] As described above, the handheld device 10 is structured such that the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50 are shared by the OCT measuring device A and the surface shape measuring device B.

[0069] A method in which the dental optical measuring device 1 having the handset 10 structured as described above performs a measurement will be described.

[0070] First, the control device 3 controls the light sources 20 (20a, 20b) to emit outgoing light Lb when a user inputs a menu screen displayed on the display device 2 to start the measurement.

[0071] The OCT measurement light LbA emitted from the light source 20a is guided to the light splitting / interference region 70 and split into the reference light LbA1 and the illumination measurement light LbA2 by the light splitting / interference region 70. The illumination measurement light LbA2 and the surface measurement light LbB are introduced into the handheld device 10 through the entrance regions 11. The reference light LbA obtained as a result of the splitting performed by the light splitting / interference region 70 passes through the light transmission / reception path 71 and is directed onto the reflecting mirror 72. The reflected light RbA obtained by the reference light LbA reflected by the reflecting mirror passes through the light transmission / reception path 71 and is guided to the light splitting / interference region 70.

[0072] As described above, the outgoing light Lb introduced into the handset 10 passes through the mirrors, the beam combiner and beam splitter 12, the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50, exits toward the location of the diagnostic object 100, is backscattered by the surface and the interior of the location of the diagnostic object 100, and enters the handset 10 as scattered light Sb (SbA, SbB) through the incoming / outgoing opening 50.

[0073] As described above, the scattered light SbB entering the incoming / outgoing opening 50 passes through the light transmission / reception path 40, the mirrors, the beam combiner and beam splitter 12, and the lens 13 in the handset 10 and is directed to the light receiving device 60b. The light receiving device 60b, having received the scattered light SbB, converts the received scattered light SbB into an electrical signal and transmits the electrical signal to the control device 3.

[0074] The scattered light LbA incident into the incoming / outgoing opening 50 passes through the light transmission / reception path 40, the scanning mirror 30, the mirrors, the beam combiner and the beam splitter 12, is guided out of the handset 10 from the entrance region 11a and guided to the light splitting / interference region 70.

[0075] The scattered light SbA guided to the light splitting / interference region 70 and the light RbA reflected by the reflecting mirror 72, which is located at a distance from the light splitting / interference region 70 by a distance equal to the distance between the light splitting / interference region 70 and the location of the diagnostic object 100, are used to generate the coherent light Kb with the light splitting / interference region. The coherent light Kb is guided to the light receiving device 60a.

[0076] The light receiving device 60a, which has received the coherent light Kb, converts the intensity of the coherent light Kb into an electrical signal and transmits the electrical signal to the control device 3.

[0077] The surface of the location of the diagnostic object 100 is scanned with the outgoing light Lb while controlling the orientation of the scanning mirror 30. The light SbB scattered at each of the parts scanned with the outgoing light Lb and the coherent light Kb are each converted into electrical signals. The control section 3 receives the electrical signals from the light receiving devices 60b and 60a, respectively, and displays a measured image, which is a result of the measurement at the location of the diagnostic object 100, on the display device 2 based on the received electrical signals.

[0078] This is described more specifically. Among the results obtained by scanning with the outgoing light Lb, the electrical signal obtained as a result of converting the scattered light SbB is used to generate information about the three-dimensional shape of the location of the diagnostic object 100. The electrical signal obtained as a result of converting the coherent light Kb is used to generate information about the interior of the location of the diagnostic object 100. The information about the three-dimensional shape and the interior information are displayed on the display device 2.

[0079] As described above, the dental optical measuring device 1 directs the outgoing light Lb from the handheld device 10 toward the location of the diagnostic object 100, and can thus generate three-dimensional spatial data resulting from the synthesis of the three-dimensional shape information and the information about the interior of the location of the diagnostic object 100. Therefore, the dental optical measuring device 1 can acquire both optical coherence tomography information and three-dimensional shape information, while the dental optical measuring device 1 has a compact structure and eliminates the need for device replacement.

[0080] This will be described in more detail. The display device 2, the control device 3, the scanning mirror 30, the light transmission / reception path 40, and the inlet / outlet opening 50 are comprised of the OCT measuring device A and the surface shape measuring device B as the display device 2a / 2b, the control device 3a / 3b, the scanning mirror 30a / 30b, the light transmission / reception path 40a / 40b, and the inlet / outlet opening 50a / 50b. Due to this, the dental optical measuring device 1 can be more compact compared to the case where an optical coherence tomography information acquisition device and a three-dimensional shape information acquisition device are separately constructed.

[0081] At least the scanning mirror 30, the light transmission / reception path 40, and the inlet / outlet opening 50 are included in the handheld device 10 operable to diagnose the location of the diagnostic object 100. Therefore, both the optical coherence tomography information and the three-dimensional shape information can be obtained with the handheld device 10 without requiring any device exchange.

[0082] Specifically, a dental optical measuring device 1 can acquire high-precision three-dimensional spatial data including information about the surface and interior of the location of the diagnostic object, in which the information about the interior of the diagnostic object based on the optical coherence tomography information and the surface information about the location of the diagnostic object based on the three-dimensional shape information complement each other. Of these data, only the surface data can be extracted and used as impression data. The interior data is suitable for high-precision diagnosis of incipient dental caries, root fractures, or the like. The interior data is also suitable for designing an upper structure for embedding an implant and simulating implantation.

[0083] The light transmission / reception path 40 for guiding the outgoing light Lb from the scanning mirror 30 to the incoming / outgoing aperture 50 and for guiding the scattered light Lb incident on the incoming / outgoing aperture 50 includes the objective lenses 40L. These optical paths guide light more stably than an optical path formed from, for example, a light guide or the like. The refractive index, light guide ratio, and the like of the lenses can be adjusted to provide a predetermined performance level.

[0084] The surface shape measuring device B scans the location of the diagnostic object 100 with the surface measurement light LbB, illuminates it, and receives the scattered light SbB obtained as a result of the backscattered surface measurement light LbB directed onto the location of the diagnostic object 100 in an oblique direction, thereby obtaining information about the three-dimensional shape of the surface of the location of the diagnostic object 100 through triangulation. The surface shape measuring device B passes the light through the surface measurement light receiving parts 40b (40b1, 40b2) that are eccentric with respect to the center of the objective lenses 40L, and can therefore obtain accurate information about the three-dimensional shape.

[0085] The light source 20b of the surface shape measuring device B and the light source 20a of the OCT measuring device A are provided separately. Therefore, the illumination measurement light LbA2 and the surface measurement light LbB can be emitted for measurement according to the respective measurement type. Since the light source 20b of the surface shape measuring device B and the light source 20a of the OCT measuring device A are provided separately, the illumination measurement light LbA2 and the surface measurement light LbB can be emitted from the light sources 20a and 20b at the same time. Therefore, the optical coherence tomography information and the three-dimensional shape information can be obtained simultaneously.

[0086] The light splitting / interference portion 70 splits the OCT measurement light LbA into the illumination measurement light LbA2 and the reference light LbA1, and further causes interference of the reflected light RbA and the scattered light SbA to generate the coherent light Kb. Therefore, the dental optical measuring device 1 can be made more compact compared to the case where a light splitting portion for splitting the OCT measurement light LbA and a light interference portion for generating the coherent light Kb are individually provided.

[0087] In the above description, the scanning mirror 30, the light transmission / reception path 40, the incoming / outgoing opening 50, and the light receiving device 60b are provided in the handset 10 of the dental measuring device 1, and the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50 are shared by the OCT measuring device A and the surface shape measuring device B.Alternatively, as long as the length of the optical path from the light splitting / interference portion 70 to the reflecting mirror 72 can be set to the same length as the length of the optical path from the light splitting / interference portion via the scanning mirror 30 and the light transmitting / receiving path 40 to the location of the diagnosis object 100, the handset 10 may include the light splitting / interference portion 70, the light transmitting / receiving path 71, and the reflecting mirror 72 in addition to the scanning mirror 30, the light transmitting / receiving path 40, the incoming / outgoing opening 50, and the light receiving device 60b, or may further include the light sources 20 as shown by a plurality of chain lines with a dot in FIG. Fig. 1. The handset 10 may further include the light receiving device 60a in addition to the elements described above. Alternatively, the light receiving device 60b may be located outside the handset 10.

[0088] For example, the handheld device 10 may include the scanning mirror 30, the light splitting / interference region 70, the light transmission / reception path 40, the incoming / outgoing opening 50, the reflecting mirror 72, and the light receiving device 60a of the OCT measurement device A. Due to this, the OCT measurement light LbA passed through the scanning mirror 30 can be split by the light splitting / interference region 70 and directed to the location of the diagnostic object 100 via the light transmission / reception path 40 and the incoming / outgoing opening 50, and the reflected light RbA can also be obtained from the reference light LbA1 directed to the reflecting mirror 72. The interference between these two light components is caused by the light splitting / interference region 70, and the generated coherent light Kb is received by the light receiving device 60a.Thus, the dental optical measuring device can obtain the information of optical coherence tomography and can also be more compact and have higher precision.

[0089] Fig. Fig. 6(a) is a schematic structural view of a dental optical measuring device 1a of another embodiment. As shown in Fig. As shown in Figure 6(a), in the dental optical measuring device 1a, unlike the dental optical measuring device 1, a light source 20 is shared by the OCT measuring device A and the surface shape measuring device B. In this configuration, the light splitting / interference section 70 splits the outgoing light Lb emitted from the light source 20 into the reference light LbA1 and the illumination measurement light LbA2, and the OCT measuring device A and the surface shape measuring device B both use the illumination measurement light LbA2 for measurements. The light source 20 emits the outgoing light Lb having a wavelength suitable for both the measurements performed with the OCT measuring device A and the measurements performed with the surface shape measuring device B.

[0090] Furthermore, in the dental optical measuring device 1a, the handheld device 10 may include the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50. Alternatively, the handheld device 10 may include any of various other elements, for example, the light splitting / interference region 70, the light transmission / reception path 71, and the reflecting mirror 72 in addition to the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50, for example, the light source 20a in addition to these elements, or even the light receiving device 60 in addition to these elements. Also, in the dental optical measuring device 1a, it is necessary to equate the length of the optical path from the light splitting / interference region 70 to the reflecting mirror 72 with the length of the optical path from the light splitting / interference region 70 to the location of the diagnostic object 100.

[0091] Similar to the dental optical measuring device 1, the dental optical measuring device 1a has some elements shared by the OCT measuring device A and the surface shape measuring device B, and has a part of these elements within the handheld device 10. Therefore, the dental optical measuring device 1a achieves the same effect as the dental optical measuring device 1. In addition, the dental optical measuring device 1a has a larger number of elements shared by the devices A and B than the dental optical measuring device 1, and therefore achieves a greater effect.

[0092] Fig. Fig. 6(b) is a schematic structural view of a dental optical measuring device 1b of another embodiment. As shown in Fig. 6(b), in the dental optical measuring device 1b, unlike the dental optical measuring device 1 having the light splitting / interference portion 70, a light splitting portion 70a for splitting the OCT measurement light LbA into the reference light LbA1 and the illumination measurement light LbA2 and a light interference portion 70b for causing interference of the reflected light RbA and the scattered light SbA to generate the coherent light Kb are individually provided.

[0093] In this configuration, the outgoing light Lb emitted from the light source 20 is split into the reference light LbA1 and the illumination measurement light LbA2 by the light splitting region 70a, and the reference light LbA1 is directed onto the reflecting mirror 72 via the light transmission / reception path 71. The light RbA reflected by the reflecting mirror 72 is guided to the light interference region 70b via the light transmission / reception path 71. The scattered light SbA guided through the light transmission / reception path 40 is also guided to the light interference region 70b. The light interference region 70b causes interference between the reflected light RbA and the scattered light SbA to generate coherent light Kb, and the coherent light Kb is guided to the light receiving device 60a.

[0094] In the case of the dental optical measuring device 1b, the length of the optical path from the light splitting region 70a to the location of the diagnostic object 100 is set to the same length as the length of the optical path from the light splitting region 70a to the reflecting mirror 72, and the length of the optical path from the location of the diagnostic object 100 to the light interference region 70b is set to the same length as the length of the optical path from the reflecting mirror 70 to the light interference region 70b.

[0095] Similar to the dental optical measuring device 1, the dental optical measuring device 1b has some elements shared by the OCT measuring device A and the surface shape measuring device B. Therefore, the dental optical measuring device 1b achieves the same effect as the dental optical measuring device 1.

[0096] Similar to the dental optical measuring device 1, in the dental optical measuring device 1b, the scanning mirror 30, the light transmission / reception path 40, the incoming / outgoing opening 50, and the light receiving device 60b are also provided by the handheld device 10, and the scanning mirror 30, the light transmission / reception path 40, and the incoming / outgoing opening 50 are shared by the OCT measuring device A and the surface shape measuring device B. Alternatively,as long as the length of the optical path from the light splitting area 70a to the reflecting mirror 72 can be set to the same length as the length of the optical path from the light splitting area 70a via the scanning mirror 30 and the light transmission / reception path 40 to the location of the diagnostic object 100, and as long as the length of the optical path from the location of the diagnostic object 100 via the scanning mirror 30 and the light transmission / reception path 40 to the light interference area 70b can be set to the same length as the length of the optical path from the reflecting mirror 72 to the light interference area 70b, the handheld device comprises the light splitting area 70a, the light interference area 70b, the light transmission / reception path 71, and the reflecting mirror 72 in addition to the scanning mirror 30 and the light transmission / reception path 40,the inlet / outlet opening 50 and the light receiving device 60b, or it may further comprise the light source 20 in addition to the above-described elements, the light transmission / reception path 71, and the reflecting mirror 72. The handset 10 may further comprise the light receiving device 60a in addition to the above-described elements. Alternatively, the light receiving device 60b may be located outside the handset 10.

[0097] Fig. Fig. 6(c) is a schematic structural view of a dental optical measuring device 1c of another embodiment. As shown in Fig. 6(c), in the dental optical measuring apparatus 1c, only the display device 2 and the control device 3 are shared by the OCT measuring device A and the surface shape measuring device B, and the other elements are provided for the OCT measuring device A and the surface shape measuring device B individually. In the dental optical measuring device 1, the light transmission / reception path 40 functions as both a light transmission path for guiding the outgoing light Lb and a light reception path for guiding the scattered light Sb. In contrast, in the dental optical measuring device 1c, light transmission paths 401 (401a, 401b), light reception paths 402 (402a, 402b), outgoing openings 501 (501a, 501b), and incoming openings 502 (502a, 502b) are individually provided for the OCT measuring device A and the surface shape measuring device B.

[0098] The surface shape measuring device B performs surface measurements of the location of the diagnostic object 100 by triangulation. The light receiving path 402b of the surface shape measuring device B is located at a position eccentric from the center of the handheld device or its vicinity such that the scattered light SbB obtained from the surface measurement light LbB directed toward the location of the diagnostic object 100 is incident on the handheld device 10 in an oblique direction.

[0099] The dental optical measuring device 1c structured as described above can obtain the internal information based on the optical coherence tomography information obtained by the OCT measuring device A and the three-dimensional shape information obtained by the surface shape measuring device B even without requiring exchange of devices by inserting the handset into the oral cavity.

[0100] Since the light source 20a and the light source 20b are provided individually, the OCT measuring device A and the surface shape measuring device B can use outgoing light LbB having a wavelength suitable for each measurement.

[0101] Similar to the dental optical measuring device 1, in the dental optical measuring device 1c, the scanning mirror 30, the light transmission paths 401, the light reception paths 402, the outgoing openings 501, the incoming openings 502, and the light reception device 60b are also provided by the hand-held device 10. Alternatively, as long as the length of the optical path from the light splitting / interference region 70 to the reflecting mirror 73 can be set to the same length as the length of the optical path from the light splitting / interference region 70 via the scanning mirror 30, the light transmission path 401 and the outgoing opening 501a to the location of the diagnosis object 100, and as long as the length of the optical path from the reflecting mirror 72 to the light splitting / interference region 70 can be set to the same length as the length of the optical path from the location of the diagnosis object 100 via the incoming opening 502a,The light receiving path 402a and the scanning mirror 30 can be adjusted to the light splitting / interference region 70. The handheld device 10 may include the light splitting / interference region 70, the light transmitting / receiving path 71, and the reflecting mirror 72 in addition to the scanning mirror 30, the light transmitting paths 401, the light receiving paths 402, the outgoing openings 501, the incoming openings 502, and the light receiving device 60b, or it may further include the light sources 20 in addition to the elements described above. The handheld device 10 may even further include the light receiving device 60a in addition to the elements described above. Alternatively, the light receiving device 60b may be located outside the handheld device 10.

[0102] In the foregoing description, the measuring device A is of the SS-OCT (swept source OCT) type. The SS-OCT measuring device A operates as follows. Wavelength-scanning laser light is used as the OCT measurement light LbA. The OCT measurement light LbA is split into the illumination measurement light LbA2 and the reference light LbA1 by the light splitting / interference section 70. The illumination measurement light LbA2 is directed onto the location of the diagnostic object 100. Interference between the reflected light RbA by the reflecting mirror 72, which has a fixed optical path length to the light splitting / interference section 70, and the scattered light SbA scattered backward by the location of the diagnostic object 100 is caused to generate coherent light Kb. Components of coherent light Kb with different wavelengths are obtained from the length-sensing laser light, converted into electrical signals and processed by Fourier transformation.This is how optical coherence tomography information is obtained. Alternatively, the measurement device A can be of the TD-OCT type (“time domain OCT”) or SD-OCT type (“spectral domain OCT”).

[0103] For example, the TD-OCT measurement device A operates as follows. Low-coherence light from a superluminescent diode is used as OCT measurement light LbA. The OCT measurement light LbA is split into the illumination measurement light LbA2 and the reference light LbA1 by the light splitting / interference section 70. The illumination measurement light LbA2 is directed toward the location of the diagnostic object 100. Interference between the reflected light RbA reflected by the reflecting mirror 72, which has a movable unit for changing the optical path length to the light splitting / interference section 70, and the scattered light SbA backscattered by the location of the diagnostic object 100 is caused to generate coherent light Kb. The reflecting mirror 72 is moved to acquire components of the coherent light Kb at locations with different optical path lengths and convert them into electrical signals.This provides information from optical coherence tomography.

[0104] In the case of the SD-OCT measuring device A, for example, the measuring device A operates as follows. Low-coherence light from a superluminescent diode is used as the OCT measurement light LbA. The OCT measurement light LbA is split into the illumination measurement light LbA2 and the reference light LbA1 by the light splitting / interference region 70. The illumination measurement light LbA2 is directed onto the location of the diagnostic object 100. Interference between the reflected light RbA reflected by the reflecting mirror 72, which has a fixed optical path length to the light splitting / interference region 70, and the scattered light SbA scattered backward by the location of the diagnostic object 100 is caused to generate the coherent light Kb. Components of the coherent light Kb are obtained at different path lengths using a spectroscope, converted into electrical components, and processed using Fourier transformation.This provides information from optical coherence tomography.

[0105] The OCT measuring device A can be of the SS-OCT, TD-OCT, or SD-OCT type. Any method of the OCT measuring device A that is suitable for the location of the diagnostic object 100, the facility environment, or the like can be used.

[0106] The surface shape measuring device B using triangulation described above may use any one of a light spot projection method (fiber optic method), a light cutout method (light slit projection method), a light pattern projection method, a space coding method, and a phase shift method.

[0107] This will be described in more detail. For example, the surface shape measuring device B using the light spot projection method (fiber optic method) operates as follows. Laser light is used as the surface measurement light LbB. The surface measurement light LbB is reflected by the scanning mirror 30 and directed toward the location of the diagnosis object 100. The scattered light SbB scattered backward from the location of the diagnosis object 100 is captured by a CCD (charge coupled device) camera, a CMOS (complementary metal oxide semiconductor) camera, or the like in a direction having an angle called a "triangulation angle" with respect to the optical axis of the laser light directed toward the location of the diagnosis object 100. Thus, a three-dimensional position at the location of the diagnosis object 100 is obtained by triangulation.The orientation of the scanning mirror 30 is changed to obtain information about the three-dimensional shape of the entire location of the diagnostic object.

[0108] The surface shape measuring device B, which uses, for example, the light slitting method (light slit projection method), operates as follows. Line-shaped light generated by passing white light or the like through a slit, using laser light for scanning, or passing laser light through a cylindrical lens is used as surface measurement light LbB. The surface measurement light LbB is reflected by the scanning mirror 30 and directed toward the location of the diagnosis object 100. The scattered light SbB scattered backward from the location of the diagnosis object 100 is captured by a CCD camera, a CMOS camera, or the like in a direction having a triangulation angle with respect to the optical axis of the line light directed toward the location of the diagnosis object 100. Thus, a three-dimensional position at the location of the diagnosis object 100 is obtained by triangulation.The orientation of the scanning mirror 30 is changed to obtain information about the three-dimensional shape of the entire location of the diagnostic object 100.

[0109] The surface shape measuring device B, which uses a light pattern projection method, operates, for example, as follows. A light pattern is projected onto the location of the diagnostic object 100. Scattered light SbB backscattered from the location of the diagnostic object 100 is captured with a CCD camera, a CMOS camera, or the like in a direction having a triangulation angle with respect to the optical axis of the light pattern directed onto the location of the diagnostic object 100. In this way, information about the three-dimensional shape of the entire location of the diagnostic object 100 is obtained.

[0110] The surface shape measuring device B, which uses the spatial coding method or the phase shift method, operates as follows. A plurality of striped light patterns are sequentially projected onto the location of the diagnostic object 100. Scattered light SbB backscattered from the location of the diagnostic object 100 is captured with a CCD camera, a CMOS camera, or the like in a direction having a triangulation angle with respect to the optical axis of the light pattern directed onto the location of the diagnostic object 100. In this way, information about the three-dimensional shape of the entire location of the diagnostic object 100 is obtained.

[0111] The surface shape measuring device B can use the triangulation method of any of the light spot projection method (fiber optic method), the light cutout method (light slit projection method), the light pattern projection method, the spatial coding method, and the phase shift method. Any method suitable for the location of the diagnostic object 100, the environment of the facility, or the like can be used in the surface shape measuring device B.

[0112] The surface shape measuring device B may use a method other than triangulation; for example, a confocal method. In the case that the surface shape measuring device B uses the confocal method, the Fig. 7 is provided. In addition to the elements of the triangulation-using surface shape measuring device B, a movable unit 42 for moving the surface measurement light transmitting / receiving part 40b and a pinhole 61 for allowing the scattered light SbB to pass therethrough are provided in front of the light receiving device 60b.

[0113] The surface shape measuring device B using the confocal method, for example, operates as follows. Laser light is used as the surface measurement light LbB. The surface measurement light LbB is reflected by the scanning mirror 30, passes through the objective lenses 40L, which have a movable unit 42 for moving the objective lenses 40L in the direction of their optical axis, and is directed onto the location of the diagnostic object 100. As shown in Fig.As shown in Figure 3(b), the scattered light SbB scattered backward in the same direction as the optical axis of the surface measurement light LbB directed at the location of the diagnostic object 100 is collected at the pinhole 61 and detected by, for example, a photodiode or a photomultiplier tube. The scattered light SbB originating from a position other than the focal point of the objective lenses 40L is blocked by the pinhole 61, and the objective lenses 40L are moved in the direction of their optical axes by the movable unit 42. In this way, the position of a surface of an object, which is the location of the diagnostic object 100, can be detected. By performing scanning with the scanning mirror 30, information about the three-dimensional surface of the location of the diagnostic object 100 is obtained.

[0114] In the case where the light transmission / reception path 40 is moved together with the OCT light transmission / reception path 40a and the surface measurement light transmission / reception part 40b by the movable unit 42, it is necessary that the length of the optical path from the light splitting / interference region 70, to which the reference light LbA1 is directed, to the reflecting mirror 72 be set to the same length as the length of the optical path of the illumination measurement light LbA2 from the light splitting / interference region 70 via the scanning mirror 30, the light transmission / reception part 40, and the inlet / outlet opening 50 to the location of the diagnosis object 100. Therefore, a movable unit is provided for moving the reflecting mirror 73 in synchronization with the movement of the light transmission / reception path 40 by the movable unit 42.

[0115] The surface measurement can be performed using a TOF (time of flight) method, which measures the time required for the scattered light SbB scattered at the location of the diagnostic object 100 to return. Alternatively, the surface measurement can be performed using a focal point method, which acquires an image of the location of the diagnostic object 100 and measures the focal position.

[0116] In the above description, the scanning mirror is provided as one element of the dental optical measuring device. The dental optical measuring device may include one scanning mirror that performs biaxial scanning or two scanning mirrors, each performing uniaxial scanning. In the case where the scanning mirror is shared by the OCT measuring device and the surface shape measuring device, one scanning mirror that performs biaxial scanning may be shared, or two scanning mirrors that each perform uniaxial scanning may be shared. Alternatively, one scanning mirror that performs uniaxial scanning may be shared, while one scanning mirror that performs uniaxial scanning is provided for the OCT measuring device and another scanning mirror that performs uniaxial scanning is provided for the surface shape measuring device.

[0117] If the scanning mirror is not shared between the OCT measuring device and the surface shape measuring device, two scanning mirrors each performing biaxial scanning or four scanning mirrors each performing single-axis scanning can be provided. The scanning mirror performing biaxial scanning can be, for example, a MEMS (Micro Electro Mechanical System) mirror. The scanning mirror performing single-axis scanning can be, for example, a MEMS mirror, a galvanic mirror, or similar.

[0118] The measurement result display area of ​​the present invention corresponds to the display area 2, 2a, 2b of the embodiments; and similarly, corresponds to the measurement control range of the control device 3, 3a, 3b; the measurement light corresponds to the outgoing light Lb, the illumination measurement light LbA2, the surface measurement light LbB; the measurement light emission range corresponds to the light source 20, 20a, 20b; the target of the measurement corresponds to the location of the diagnostic object 100, which includes the tooth 101 and the gum 102; the outgoing opening and the incoming opening correspond to the incoming / outgoing opening 50, 50a, 50b; the light transmission path and the light reception path correspond to the light transmission / reception path 40, 40A, 40B; the light receiving area corresponds to the light receiving device 60, 60a, 60b; the optical three-dimensional surface measuring system structure corresponds to the surface shape measuring device B; the light splitting area corresponds to the light splitting area 70a; the light interference area corresponds to the light interference area 70b; the light splitting area and the light interference area and the light splitting area correspond to the light splitting / interference area 70; the reflected reference light corresponds to the reflected light RbA; the coherent light receiving area corresponds to the light receiving device 60a; the optical coherence tomography measurement system structure corresponds to OCT measurement device A; the diagnostic tool corresponds to the handset 10; the lens system light guide path corresponds to the light transmission / reception path 40; the optical axis corresponds to the OCT light transmission / reception path 40a; the scattered light corresponds to the scattered light SbA reflected or scattered at the surface or inside the location of the diagnostic object 100, the scattered light SbB reflected or scattered at the surface and inside the location of the diagnostic object 100; and the eccentric position corresponds to the surface measurement light transmitting / receiving part 40b.

[0119] However, the present invention is not limited to any of the embodiments described above and can be implemented in many other embodiments.

[0120] For example, in the above description, the OCT measurement device is a Fourier domain system. Alternatively, OCT measurement device A can also be a time domain system. [Industrial applicability]

[0121] The present invention is suitable for various optical measuring devices suitable for obtaining both optical coherence tomography information and information about the three-dimensional shape of a living organism by laser light, for example, to take impressions. [Description of reference symbols] 1 dental optical measuring device 2, 2a, 2b display device 3, 3a, 3b control device 10 Handpiece 20, 20a, 20b light source 30, 30a, 30b scanning mirror 40, 40A, 40B Light transmission / reception path 50 incoming / outgoing opening 50a incoming / outgoing opening for OCT 50b inlet / outlet opening for surface measurements 60, 60a, 60b Light receiving device 70 light splitting / interference area 70a Light splitting area 70b Light interference area 72 reflecting mirror 100 Location of the diagnostic object 101 tooth 102 Gums Kb coherent light Lb outgoing light LbA OCT measurement light LbA1 reference light LbA2 Illumination measurement light LbB surface measurement light RbA reflected light Sb, SbA, SbB scattered light A OCT measuring device B Surface form measuring device

Claims

[1] A dental optical measuring device comprising: an optical three-dimensional surface measuring system structure with a measurement result display area for displaying at least one measurement result, a measurement control area for controlling a measurement, a measurement light emission area for emitting measurement light, a scanning mirror suitable for scanning with the measuring light, an opening through which the measuring light is directed onto a measurement target, a light transmission path for guiding the measurement light to the outgoing opening, an incoming opening onto which the measurement light directed from the outgoing opening is incident after being scattered at the measurement target, a light receiving path for guiding the scattered light incident on the incoming opening and a light receiving region for receiving the scattered light passed through the light receiving path; and an optical coherence tomography measurement system structure with a measurement result display area for displaying at least one measurement result, a measurement control area for controlling a measurement, a measurement light emission area for emitting measurement light, a light splitting area for splitting the measurement light into measurement light and reference light, a scanning mirror suitable for scanning with the measuring light, an opening through which the measuring light is directed onto the target of the measurement, a light transmission path for guiding the measurement light to the outgoing opening, an incoming opening onto which the measurement light directed from the outgoing opening falls after being scattered at the measurement target, a light receiving path for guiding the scattered light incident on the incoming opening, a reflecting mirror for reflecting the reference light obtained as a result of the division carried out by the light division region, a light interference region for generating interference of the light reflected by the reflecting mirror and the scattered light and a coherent light receiving region for receiving a coherent light generated by the interference performed by the light interference region; wherein: the light transmission path and the light reception path comprise a lens system light guide path for guiding the measurement light to the outgoing opening and for guiding the scattered light from the incoming opening; the light transmission path and the light reception path of the optical coherence tomography measurement system structure are located on an optical axis of the lens system light guide path; the light transmission path and the light reception path of the three-dimensional surface measurement system optical structure are located at an eccentric position that is eccentric from the optical axis of the lens system light guide path; the optical three-dimensional surface measurement system structure and the optical coherence tomography measurement system structure share at least one of the measurement result display area, the measurement control area, the measurement light emission area, the scanning mirror, the light transmission path, the outgoing opening, the incoming opening, and the light receiving path; at least the scanning mirror, the light transmission path, the outgoing opening, the incoming opening and the light receiving path are shown in a diagnostic tool suitable for making a diagnosis about the measurement target. [2] A dental optical measuring device according to claim 1, wherein the three-dimensional surface optical measuring system structure and the optical coherence tomography measuring system structure share the scanning mirror, the light transmission path, the outgoing opening, the incoming opening and the light receiving path. [3] A dental optical measuring device according to any one of claims 1 to 2, wherein: the measurement light emission region of the optical three-dimensional surface measuring system structure and the measurement light emission region of the optical coherence tomography measuring system structure are formed separately. [4] A dental optical measuring device according to any one of claims 1 to 3, wherein the light splitting portion and the light interference portion are integrally formed as a light splitting / interference portion for splitting the measurement light into the measurement light and the reference light and causing interference of the reflected light and the scattered light to generate coherent light. [5] A dental optical measuring device according to claim 4, wherein the scanning mirror, the light splitting / interference portion, the light transmitting path, the outgoing opening, the light receiving path, the reflecting mirror, the coherent light receiving portion, and the incoming opening of the optical coherence tomography measuring system structure are comprised of a diagnostic tool. [6] A dental optical measuring / diagnostic tool suitable for making a diagnosis by means of a measuring light directed at a measurement target, comprising: an optical three-dimensional surface measuring system structure with a measurement light emission area for emitting measurement light, a scanning mirror suitable for scanning with the measuring light, an opening through which the measuring light is directed onto the target of the measurement, a light transmission path for guiding the measurement light to the outgoing opening, an incoming aperture onto which the measurement light directed from the outgoing aperture falls after being scattered by the measurement target, a light receiving path for guiding the scattered light incident on the incoming opening and a light receiving region for receiving the scattered light guided from the light receiving path; and an optical coherence tomography measuring system structure with a measurement light emission area for emitting measurement light, a light splitting area for splitting the measurement light into measurement light and reference light, a scanning mirror suitable for scanning with the measuring light, an opening through which the measuring light is directed onto the target of the measurement, a light transmission path for guiding the measurement light to the outgoing opening, a light receiving path for guiding the scattered light obtained as a result of the measurement light directed out from the outgoing opening, scattered by the measurement target, and incident on the incoming opening, a reflecting mirror for reflecting the reference light obtained as a result of the division carried out by the light division region, a light interference region for causing interference of the reference light reflected from the reflecting mirror and the scattered light, and a coherent light receiving region for receiving a coherent light generated by the interference performed by the light interference region; wherein: the light transmission path and the light reception path comprise a lens system light guide path for guiding the measurement light to the outgoing opening and for guiding the scattered light from the incoming opening; the light transmission path and the light reception path of the optical coherence tomography measurement system structure are located on an optical axis of the lens system light guide path; the light transmission path and the light reception path of the three-dimensional surface measurement system optical structure are located at an eccentric position that is eccentric from the optical axis of the lens system light guide path; at least the scanning mirrors, the light transmission paths, the outgoing openings, the incoming openings and the light receiving paths are provided by a tool body suitable for making a diagnosis about the measurement target; and the optical three-dimensional surface measurement system structure and the optical coherence tomography measurement system structure share at least one of the measurement result display area, the measurement control area, the measurement light emission area, the scanning mirror, the light transmission path, the outgoing opening, the incoming opening, and the light receiving path. [7] A dental optical measuring / diagnostic tool according to claim 6, wherein the three-dimensional surface optical measuring system structure and the optical coherence tomography measuring system structure share the scanning mirror, the light transmission path, the outgoing opening, the incoming opening and the light receiving path. [8] A dental optical measuring / diagnostic tool according to any one of claims 6 to 7, wherein the light splitting portion and the light interference portion are integrally formed as a light splitting / interference portion for splitting the measurement light into the measurement light and the reference light and causing interference of the reflected reference light and the scattered light to generate coherent light. [9] A dental optical measuring / diagnostic tool according to claim 8, wherein the scanning mirror, the light splitting / interference portion, the light transmitting path, the outgoing opening, the light receiving path, the reflecting mirror, the coherent light receiving portion, and the incoming opening of the optical coherence tomography measuring system structure are comprised by the main body of the tool body.

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