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    • 专利摘要:
    APPARATUS TO DETECT PHOTOTHERMAL RADIATION FROM AN OBJECT, AND, SYSTEM. An apparatus is provided to perform photothermal measurements on an object. The device, which can be provided as a handpiece, houses optical components including a laser, an infrared detector, a dichroic beam separator, and beam focusing and targeting optics for delivering a laser beam to the measured object, and the collection of photothermal radiation from it. Some of the optical components can be provided on an optical bench that is directly attached to a portion of the thermally conductive tip for the passive heat dissipation of internal, optical components. The apparatus may additionally include an optical sampling element and a photodetector for detecting luminescence, and a camera for obtaining an image of the object during a diagnostic procedure. The device can be used to scan a tooth to determine an oral health status of the tooth.
    公开号:BR112012029068B1
    申请号:R112012029068-1
    申请日:2011-05-13
    公开日:2020-10-27
    发明作者:Jin-Seok Jeon；Andreas Mandelis；Stephen Abrams；Anna Matvienko；Koneswaran Sivagurunathan；Josh Silvertown；Adam Hellen
    申请人:Quantum Dental Technologies Inc.；
    IPC主号:
    专利说明:

    CROSS REFERENCE TO RELATED ORDER
    [001] This application claims priority for U.S. provisional application No. 61 / 334,436 entitled ’’ Handpiece with Integrated Optical System for Photothermal Radiometry and Luminescence Measurements "and filed on May 13, 2010, the contents of which are hereby incorporated by reference. BACKGROUND OF THE INVENTION
    [002] The present disclosure concerns detection methods in oral health care.
    [003] With the widespread use of fluoride, the prevalence of dental caries has been considerably reduced. However, the development of a non-invasive, non-contact technique that can detect and monitor early demineralization or small carious lesions on the enamel, dentin, root surface, or around them, or around the margins of dental restorations, is essential for clinical management of this problem.
    [004] In dentistry, the goal of recent scientific research has been the use of laser fluorescence for detecting tooth demineralization and tooth decay (eg, enamel and / or root), dental deposits and dental calculations, and quantitative depth analysis and size of the lesion, as well as the mineral composition of the enamel [M. L. Sinyaeva, Ad. A. Mamedov, S. Yu. Vasilchenko, A. I. Volkova, and V. B. Loschenov, 2003, "Fluorescence Diagnostics in Dentistry", Laser Physics, 14, No. 8, 2004, pp. 1,132-1,140]. These principles have been used to develop numerous fluorescence-based technologies, such as QLF ™ and DIAGNOdent ™ diagnostic devices.
    [005] UV radiation (488 nm) has been used to examine tooth enamel [Susan M. Higham, Neil Pender, Elbert de Josselin de Jong, and Philip W. Smith, 2009. Journal of Applied Physics 105, 102048, R. Hibst and R. Paulus, Proc. SPIE 3593, 141 (1999)]. Studies showed that healthy enamel autofluorescence peaked at a wavelength of 533 nm, while the autofluorescence of carious tissue was shifted to red at 40 nm. It was also demonstrated that the intensity of autofluorescence of carious zones was an order of magnitude lower than the intensity of autofluorescence of a healthy tooth, despite the fact that the absorbance of the carious zone in the excitation wavelength was significantly higher.
    [006] The reduction in fluorescence when enamel demineralizes or when a carious lesion has been developed has been attributed to the increase in the porosity of carious lesions, when compared to healthy enamel. There is an associated intake of water and a decrease in the refractive index of the lesion, resulting in greater dispersion and a decrease in the length of the light path, absorption and autofluorescence [H. Bjelkhagan, F. Sundstrom, B. Angmar-Mansson, and H. Ryder, Swed Dent. J. 6, 1982].
    [007] At long wavelengths of excitation, the intensity of autofluorescence of a carious cavity may be greater than the intensity of autofluorescence of healthy tissue [R. Hibst et al.]. For excitation wavelengths of 640 or 655 nm, the intensity of integral autofluorescence (at wavelengths greater than 680 nm) of a carious lesion could be approximately an order of magnitude greater than the corresponding integral autofluorescence intensity of the healthy enamel. There is some indication that the fluorescence induced at these wavelengths results from the excitation of fluorescent fluorophores from bacterial metabolites. These fluorophores are considered to originate from porphyrins found in some bacterial species [S. M. Higham et al.].
    [008] More recently, a new system has been developed based on the combination of laser-induced fluorescence and photothermal radiometry. The system, commercially available as The Canary Dental Caries Detection System ™, which examines the luminescence and photothermal effect (PTR-LUM) of laser light on a tooth, described in US patent application No. 2007/0021670, entitled "Method and Apparatus Using Infrared Photothermal Radiometry (PTR) and Modulated Laser Luminescence (LUM) for Diagnostics of Defects in Teeth ", deposited on July 18, 2006. The laser is non-invasive and can detect tooth decay of a fraction of a millimeter in size and up to five millimeters below the tooth surface. When pulses of laser light are focused on a tooth, the tooth glows and releases heat. By analyzing the light emitted and the heat signatures of the tooth, very accurate information regarding the condition of the tooth can be obtained, including signs of early demineralization (lesions) of the enamel [Nicolaides, L, Mandelis, A., Abrams, SH, "Novel Dental Dynamic Depth Profilometric Imaging using Simultaneous Frequency Domain Infrared Phototermic Radiometry and Laser Luminescence", Journal of Biomedical Optics, 2000, January, Volume 5, # 1, pages 31 - 39, Jeon, RJ, Han, C, Mandelis, A ., Sanchez, V., Abrams, SH, "Non-intrusive, Non-contacting Frequency-Domain Fotothermic Radiometry and Luminescence Depth Profilometry of Carious and Artificial Sub-surface Lesions in Human Teeth," Journal of Biomedical Optics 2004, July - August , 9, # 4, 809 - 81, Jeon RJ, Hellen A., Matvienko A., Mandelis A., Abrams SH, Amaechi BT, In vitro Detection and Quantification of Enamel and Caries Root Using Infrared Fotothermal Radiometry and Modulated Luminescence. Journal of Biomedical Optics 13 (3), 048803, 2008]. As an injury shines, there is a corresponding change in the signal. As remineralization progresses, an inversion of the signal indicates an improvement in the condition of the tooth. By changing the frequency of the signal, it is possible to probe up to 5 mm below the tooth surface. Low frequency signals can penetrate defects and lesions below the tooth surface.
    [009] A significant drawback with the aforementioned systems is the complex and expensive optical delivery systems that are typically needed. In addition, some systems involve a handpiece that is optically attached to a remote detector and laser source unit via an expensive fiber bundle. This results in numerous inconveniences, including cost, complexity and inconvenience of use because of the weight of the cables that protect the fiber bundles. SUMMARY OF THE INVENTION
    [010] An apparatus is provided to perform photothermal measurements on a sample, such as a tooth surface. The device, which can be provided in the form of a handpiece, houses optical components including a laser, an infrared detector, a dichroic beam separator, and beam focusing and targeting optics for delivering a laser beam to the measured sample , and the collection of photothermal radiation from it. Some of the optical components can be provided on an optical bench that is directly attached to a portion of the thermally conductive tip for the passive heat dissipation of internal optical components. The handpiece may include an optical beam sampling element and a photodetector for detecting luminescence, and a camera for taking an image of a sample during a measurement.
    [011] In this way, in one aspect, an apparatus is provided to detect photothermal radiation from an object, the apparatus comprising: an elongated housing; a laser to produce a laser beam within the housing; a focusing element positioned to focus the laser beam through an opening in a distal portion of the housing and on a surface of the object, and to collect photothermal radiation generated within the object in response to the laser beam; and a dichroic beam separator positioned within the housing to spatially separate photothermal radiation from the laser beam; and an infrared detector provided inside the housing to detect photothermal radiation.
    [012] An additional understanding of the functional and advantageous aspects of the disclosure can be accomplished by reference to the detailed description and drawings below. BRIEF DESCRIPTION OF THE DRAWINGS
    [013] Modalities will now be described, by way of example only, with reference to the drawings, where:
    [014] Figure 1 provides an isometric view of an oral health diagnostic handpiece for use in measuring photothermal radiometry (PTR) and luminescence (LUM) of a tooth surface.
    [015] Figure 2 provides views (a) planar, (b) broad and (c) side of the oral health diagnostic handpiece shown in figure 1.
    [016] Figures 3 (a) and (b) provide cross-sectional views of the oral health diagnostic handpiece shown in figure 1.
    [017] Figure 4 is a cross-sectional view of the oral health diagnostic handpiece in which the optical bench is shown in detail.
    [018] Figures 5 (a) - (d) show several cross-sectional views of the oral health diagnostic handpiece shown in figure 1, where the views are shown in a plane perpendicular to the longitudinal axis of the handpiece.
    [019] Figure 6 (a) shows a modality of a control and processing unit for use with the handpiece, and figure 6 (b) shows a photograph of the handpiece, control and processing unit, and others system accessories.
    [020] Figure 7 illustrates the operation of a camera integrated in the tip portion of the handpiece.
    [021] Figure 8 shows a protective tip that is received slidingly at the tip portion of the handpiece.
    [022] Figure 9 shows a calibration device for use with the handpiece. DETAILED DESCRIPTION OF THE INVENTION
    [023] Various modalities and aspects of the disclosure will be described with reference to the details discussed below. The following description and drawings are illustrative of the disclosure and should not be construed as limiting the disclosure. Numerous specific details are described to provide a general understanding of various modalities of the present disclosure. However, in certain cases, well-known or conventional details are not described in order to provide a concise discussion of the modalities of the present disclosure.
    [024] In the form used here, the terms, "comprises" and "comprising" must be interpreted in an inclusive and broad, and not exclusive. Specifically, when used in the specification and claims, the terms, "comprises" and "comprising" and their variations mean that specific features, steps or components are included. These terms should not be interpreted to exclude the presence of other resources, steps or components.
    [025] In the form used here, the term "exemplary" means "serving as an example, case or illustration," and should not be interpreted as preferred or advantageous over other configurations disclosed herein.
    [026] In the form used herein, the terms "about" and "approximately", when used in conjunction with ranges of particle sizes, mixtures of mixtures or other physical properties or characteristics, should only cover slight variations that may exist at the limits top and bottom of the dimension ranges so as not to exclude modalities where on average most dimensions are satisfied, but where dimensions can statistically exist in this region. It is not intended to exclude modalities such as these from the present disclosure.
    [027] In one mode, a handpiece is provided for diagnostic measurements by photothermal radiometry (PTR) and luminescence (LUM), in which optical components are integrated into an optical bench. As discussed below, integrating optical components directly into the handpiece on an optical bench, a compact, robust and inexpensive handpiece is provided that is well suited for routine clinical use.
    [028] Figure 1 illustrates an example implementation of a PTR-LUM 100 handpiece, shown in an external isometric view, and Figure 2 provides edge, side and plan views of the handpiece. Handpiece 100 includes a body portion 110 and a tip portion 120. The tip portion 120 is attached to the body portion at a proximal end of the tip portion 120, and delivers and receives optical radiation at the distal end. The tip portion 120 slidably receives the protective shell 130, which is removably attached along an axial direction of the tip portion. Optical components, including optical sources and detectors, are mounted on an optical bench housed within handpiece 100, as further discussed below. Handpiece 100 is connected to an external processing and control device (not shown) via electrical cable 140.
    [029] An optical filter 150 is optionally provided to block scattered laser radiation and protect the operator's eyes. The filter can be snap-fit into a receiving slot for easy attachment and removal. By incorporating the optical filter directly into the handpiece, a clinician does not need to wear protective laser gloves throughout a scanning or diagnostic procedure, and can easily see a patient's oral anatomy by moving the handpiece to remove the handpiece. a direct line of sight. This feature is clinically appropriate because it is often important for a clinician to see oral anatomy in true colors to aid in a diagnosis or guide in a diagnostic procedure.
    [030] Referring to figure 2, handpiece 100 can be used to communicate with the control and processing unit (described further below) using buttons 160 located above the body portion 1 10. For example, a User can press a button to start and / or end a measurement or series of measurements. Buttons 160, or other input and / or control elements, can be fitted to handpiece 100 in such a way that a fluid-tight seal is provided, preventing leakage of fluids into the handpiece.
    [031] As shown in figure 2, the tip portion 120 can be attached to the body portion 110 by fasteners 122 and 124 that are received in grooves 128 provided in the tip portion (only a single groove is shown in figure 2) and match a threaded hole in the body portion. In this way, the tip portion does not need to be attached to the body portion via the internal optical bench, as shown further below. An internal O-ring can be employed to provide a seal between body portion 110 and tip portion 120.
    [032] The sample handpiece provides a lightweight ergonomic design that is convenient and well adapted for clinical use. By accommodating all optical components (for example, a diode and laser detectors) within the body and tip portions of the handpiece, the need to deliver and receive optical radiation in the handpiece via optical fiber bundles is eliminated , thus allowing the device to be connected to the control and processing apparatus via a simple, flexible, inexpensive and light electrical cable (the cable can accommodate multiple electrical wires to carry various control and detected signals and energy). In addition, the use of an electrical cable, as opposed to an optical cable, decreases the minimum cable bending radius, allowing the handpiece to be manipulated in a wider range of movements and directions during a clinical procedure. Shielding can be placed over the cable to minimize electrical interference with the signal as it is transmitted over the cable.
    [033] In one embodiment, handpiece 100 has a size that is small enough to allow sweeping of teeth into the mouth of a child or an adult. In addition, the handpiece design protects optical elements from damage during normal use. As shown in figure 2, the tip piece 120 can be removed from the body part 110 using fasteners 122 and 124, which allow efficient fabrication and repair in the field.
    [034] Figure 3 provides a detailed view of the internal components housed in the body portion 110 and the tip portion 120. The optical bench 200 is contained in the body portion 110, which also receives electrical cable 140 in a strain relief device 210 (additional wires, and electrical connections to the optical components, are not shown). The electrical cable 140 electrically interfaces with the detector and laser with an external control and processing apparatus to supply energy to the laser and to process signals from the detectors. The optical bench 200 has numerous optical components attached to it, which will be described further below. The tip portion 120 includes optical beam focusing components and targeting the optional beam 202 at its distal end and also houses the optional camera 230 to obtain an image of a tooth during a diagnostic procedure.
    [035] A detailed view of the folded optical apparatus contained in the body portion 10 and the tip portion 120 is shown in figure 4. Optical bench 200 supports semiconductor laser 205 and lens 210, which collects emitted laser light which is subsequently redirected by a mirror 215 for the dichroic beam separator 220. The semiconductor laser 205 can be a laser diode with a wavelength of approximately 660 nm for the simultaneous generation of luminescence and photothermal radiation from a tooth surface.
    [036] The collimated laser beam is redirected by the dichroic beam separator 220, which has provided an optical coating with high reflectivity on the incident laser beam wavelength, allowing thermal radiation to pass through. The laser beam propagates in a substantially axial direction at the tip portion 120 along beam path 225, bypassing the sampling signal collection prism 230 and meeting mirror 235 at the distal end of tip portion 120. Mirror 235 reflects the collimated laser beam towards the focusing element 240, which focuses the laser beam as it emerges at the tip portion 120. It should be understood that the laser beam does not need to exist on the device in a direction perpendicular to its axis of propagation internal.
    [037] The focusing element 240 is optically transmissive to light at the laser wavelength and at the wavelength of luminescent and photothermal radiation. In one example, the focusing element is transmissive in the visible spectrum and in the middle infrared spectrum. The focusing element 240 has a focal length suitable for focusing the laser on a desired point size. For example, a focal length of 8.6 mm produces a point size of approximately 50 micrometers on average. The focusing element 240 provides the additional role for collecting and substantially collimating both luminescent and photothermal radiation emitted by a tooth surface in response to laser irradiation. Although the focusing element 240 is shown as a transmissive optical component, it will be apparent to those skilled in the art that the focusing element 240 and mirror 235 could be replaced by a single curved mirror, such as an off-axis parabolic mirror.
    [038] Collected luminescence is directed by mirror 235 along an axis of the tip portion 120, and a portion of the collected luminescent beam encounters a beam sampling element such as a detector prism 230 (or another suitable element, such as a filter) and is directed to the optical filter 245 and the photodetector 250. The optical filter 245 removes unwanted reflected and scattered laser light, and the photodetector 250 is selected to have an adequate spectral response for the detection of the collected luminescence. In one example, photodetector 250 may be a silicon photodiode, and optical filter 245 may be a cheap colored glass filter with a bandwidth and optical density combined with wavelength and laser energy (such as the color filter high pass RG 715).
    [039] As previously noted, the focusing element 240 also collects and collimates emitted photothermal radiation, which is reflected by mirror 235 and directed to the dichroic beam separator 220. The dichroic beam separator 220 lets in infrared radiation and reflects a portion substantial amount of scattered laser light. The dichroic beam separator 220 can also substantially reflect collected luminescence.
    [040] In one embodiment, an optical absorbent element, such as an absorbent window, can be placed between the dichroic beam separator 220 and the infrared detector 260 to attenuate both collected and / or residual laser light and transmit photothermal radiation in the region spectral infrared. In one example, the dichroic beam separator may additionally incorporate an absorptive substrate. A suitable material for the absorptive substrate is a high-pass filter material, such as germanium, which absorbs light with a wavelength less than approximately 1.85 microns.
    [041] In another example embodiment, the positions of the infrared detector 260 and laser 205 can be reversed, and the dichroic beam separator 220 can have an optical coating to transmit the laser beam and luminescent radiation, and reflect photothermal radiation. In a modality like this, it is beneficial to include the absorption window described above to attenuate reflected laser energy and luminescent radiation that would otherwise be detected by the 260 infrared detector.
    [042] The dichroic beam separator transmits collected photothermal radiation, which is subsequently focused by lens 255 on the infrared detector 260. The infrared detector can be a medium sensitive infrared detector, such as a photovoltaic HgCdZnTe detector, with a sensitive spectral region covering approximately 2 to 5 pm. The 260 infrared detector can be mounted on a thermoelectric cooler for better performance and sensitivity.
    [043] As shown in figure 4, the optical components described above (with the exception of the optical components provided in the tip portion 120) are mounted on the optical bench 200. In an example implementation, the optical bench 200 is formed of a lightweight material and thermally conductive, such as aluminum.
    [044] In the example implementation shown in figure 4, the optical bench, although housed in the body portion 110, is attached to the tip portion 120, thus allowing quick and efficient heat dissipation to the tip portion 120. Thus , the tip portion 120 may also be made of a lightweight and thermally conductive material, such as aluminum. A modality like this allows the tip portion to act as an efficient air-cooled heat sink for optical components (basically the laser diode and optionally a thermoelectric cooler (TE) attached to detector 260) mounted on the optical bench 200. This feature is especially suitable for improving the performance of the thermal detector 260, which may have a noise floor that depends heavily on the temperature (as in the case of the HgCdZnTe detector of the example described above). In addition, by attaching the optical bench directly to the rigid tip portion 120, it is possible to obtain better mechanical insulation in relation to the attachment of the optical components to the body portion 110.
    [045] Figure 5 provides a series of sectional views, where each view is in a plane perpendicular to the longitudinal axis of the handpiece. Figure 5 (a) shows a section of the dichroic beam separator 220 and reflective bending mirror 215, while figure 5 (b) illustrates a section of the optical bench 200 behind the dichroic beam separator 220 and reflective mirror 215. The figure 5 (c) illustrates a cross section of the camera 300 (discussed further below) and figure 5 (d) shows a cross section of the collection optics located at the distal end of the tip portion 120, including the focusing element 240. A Figure 5 (d) also shows a cone 270 illustrating the shape of the laser beam, and a cross section of the protective shell 130 (further described below).
    [046] In order to achieve sensitive detection of photothermal radiation and laser-induced luminescence, the handpiece can interface with a photosensitive detection system such as a sync amplifier. In such a modality, the laser intensity is modulated at a desired frequency and both the detector signal and a reference signal related to the phase of the modulated laser current are provided to the synchronism amplifier. It will be apparent to those skilled in the art that other modulation methods can be used. For example, in one embodiment, the laser energy beam can be optically nicked via a mechanical cutting disk integrated into the handpiece, where the cutting disk would provide additional active cooling of the detector via forced air convection. The synchronism amplifier can be provided on a data acquisition board housed in the control and processing unit. A suitable data acquisition card to provide locking functionality is the National Instruments NI USB-6221-OEM card. Alternatively, the amplified locking can be provided separately in an additional system that interfaces with the control and processing unit.
    [047] Figure 6 (a) illustrates an example implementation of a control and processing unit 1 containing the data acquisition board and additional electronic components required for processing, user interface and optional external network connection. The control and processing unit 1 may include a processor, memory, data bus, and may include storage media, such as flash memory or a hard drive. The control and processing unit 1 is shown interfacing with handpiece 100 via cable 2. Handpiece 100 is supported on the support structure of handpiece 8, which is shaped to secure handpiece 100 when disused, and a recess 5 to protect the distal end of the tip portion 120 when handpiece 100 is attached. The control and processing unit can also include operating switch 3 and external controls 4. Figure 6 (b) shows a photograph of the control and processing unit 1, handpiece 100 and an external computing device 10, among accessories. for use with the system.
    [048] The control and processing unit 1 can be programmed to process diagnostic measurements obtained from handpiece 100. For example, the control and processing unit 1 can perform many functions, including, but not limited to, generating a numerical output associated with the tooth surface or tooth surface section examined based on the measured signals, store and / or process diagnostic data, store and / or process image data, display output images, signs or numbers, and store relative information treatment recommendations and patient information.
    [049] In one embodiment, the control and processing unit 1 processes photothermal (PTR) and luminescence (LUM) measurements received to provide a composite numerical result that is correlated with an oral health status of a swept tooth. In one embodiment, providing a single indication of unified quantitative oral health of a measurement at a given location, the data for a given measurement is stored by the control and processing unit 1 as four separate signals; the amplitude and PTR phase and amplitude and LUM phase. A unified diagnostic measurement can be obtained by combining the four measured signals. In an example implementation, signals are processed according to the following weighting formula: • PTR amplitude weighted at 45% of the total value • PTR phase weighted at 15% of the total value • LUM phase weighted at 10% of the total value 1 LUM amplitude weighted at 30% of the total value
    [050] The four readings can be compared with the readings found on the surface of the healthy enamel surface and / or a standardized piece of hydroxyapatite. The measured signal can additionally or alternatively be compared with the surface of the healthy enamel. The results of the comparison step can be provided on a fixed scale for each reading, for example, on a scale from 1 to 100 (the scales need not be the same for each type of reading), indicating the severity of a condition. The four fixed scale results can then be weighted in the manner described above, providing the operator with a rating or range (for example, on a scale of 1 -100) indicating the health of the examined area.
    [051] In another example, the reading of a single frequency can be combined as follows: (PTR amplitude x PTR phase) / (LUM amplitude x LUM phase), to create a single reading.
    [052] Error checking can be done by combining the standard deviation of each reading into a number, as follows: LUM amplitude x LUM phase x PTR amplitude x PTR phase.
    [053] The single reading ratio / combined standard deviation can then be examined and, if the ratio increases dramatically, this may be indicative of a reading error, which can then be transferred to the operator. The single reading can be transferred to the operator along with its difference from the single reading derived from examining the healthy enamel and healthy teeth.
    [054] In another example, error checking can be done by combining the standard deviation of each reading into a number as follows: 100 x {(PTR-A-std / PTR-A) 2 + (PTR-P- std / PTR-P) 2 + (LUM-A-std / LUM- A) 2 + (LUM-P-std / LUM-P) 2} 1/2
    [055] In another embodiment, a camera is additionally provided in the handpiece to obtain an image of a selected tooth. In an example configuration shown in Figure 4, camera 300 is located near the distal end of the tip portion 120. Locating the camera near the distal end of the tip portion provides numerous benefits. First, it thermally and mechanically isolates the camera from the optical bench, so that the sensor is far from the infrared detector. In this way, heat generated by the camera is basically dissipated by the thermal mass of the tip portion and does not propagate back to the infrared detector 260. Second, locating camera 300 near the distal end of the tip portion allows the use of a camera cheap with a short working distance, thus requiring minimal optical components.
    [056] Figures 4 and 7 illustrate an example modality in which the camera 300 used is a miniature CMOS image formation sensor with integrated NTSC video signal generation. The camera is effectively a “stenopeic” image formation system (with a small aperture and a fixed lens), thus providing great depth of field and angle of view, without the greater complexity and cost of image formation and redirection optics. such as mirrors and moving lenses. The very large depth of field accommodates the placement of the stenope type imaging system over a wide range of distances relative to the tooth surface. The working distance 310 can be selected in approximately 15-20 mm, providing an image forming area of approximately 10-20 mm in diameter. It should be understood that the aforementioned stenopeic camera is merely an example of a camera that can be used, and that other miniature cameras can be used to replace the stenopeic camera.
    [057] As additionally shown in figure 7, the only optical component used is a straight angular prism 305, providing a robust and simple design. The 305 prism can be omitted using a right angle camera module. In another embodiment, the camera can be placed at a greater axial distance (shown at 315) from the distal end of the tip portion 120 to improve the operator's direct line of sight of the area where the PTR-LUM measurement is made, as shown in figure 7. The displacement of the center of the imaging plane in relation to the tip edge will increase accordingly. A suitable travel distance is approximately 20 mm.
    [058] In the example implementation shown in Figure 7, the camera samples a spatial region that is spatially displaced 320 from where the laser is delivered. Spatial displacement is beneficial in that the camera's optical path does not interfere with the optical path of the PTR-LUM detection system.
    [059] Although it is possible in alternative modalities to image the tooth area directly during the scan, this would require filtering the light collected by the image formation system, which would be problematic since it would not take the actual color image of the tooth converted to image by cause of the rejection of spectral components by the filter. Correspondingly, the device can be operated in such a way that the camera is not activated at the same time as the measurement of diagnostic data, thus avoiding the collection of scattered laser light and also avoiding electrical and / or thermal cross conversion during the measurement process. . Such a scheme is also beneficial, as the activation of the camera only during use limits the generation of residual heat.
    [060] The tip portion 120 is can be equipped with an outer shell 130, shown in more detail in Figure 8. The shell 130 includes cone section 405 with a hole provided in it for the delivery of the laser beam and the collection of photothermal radiation and luminescent. The length of the cone section can be selected to maintain an adequate working distance at the tip portion 120 with respect to the focal length of the focusing element 240. The shell 130 also includes an aperture 410 that gives optical access to the integrated camera 300. The shell 130 can be snapped into the tip portion 120, for example, by means of the feature 415 and a corresponding protruding feature in the tip portion 120.
    [061] Shell 130 can be a disposable item that is used in combination with a sterile, transparent lid, such as a thin transparent material to protect the handpiece and eliminate any cross-contamination between patient. The cap fits over the tip portion 120 of the handpiece so that it does not bend or deform, thus preventing signal deflection or distortion of images from the camera.
    [062] An example cap material is a layer of transparent polymer that can be provided in the form of a bag, sheath or sock with a suitable shape to cover the tip portion 120. The cap can be disposable. The cap is first placed on the tip portion, and the protective shell 130 is subsequently placed on the lid to secure it in place between the protective shell 130 and the tip portion 120. The protective shell 130 protects the lid from accidental breakage. (drilling / tearing) of the sterile barrier. The cover is partially or substantially transparent over at least a portion of the visible or near infrared spectrum (the portion where laser light is delivered and luminescence is generated) and the medium infrared spectrum (where photothermal radiation is generated). In one example, the transmissivity of the cap is at least 75% in the spectral region of interest. In another example, the transmissivity of the cap is at least 90% in the spectral region of interest.
    [063] In an example implementation, the tip portion 120 can be provided in multiple sizes with different working distances (or focal length) from the focusing element 240. Different working distances may be suitable, depending on the clinical situation. For example, smooth surfaces can be swept with a tip portion different from the tip portion used to sweep grooves on the bite surfaces of posterior teeth or interproximal points (between teeth). In such cases, a different shell 130 can also be provided for each portion of the different tip 120, so that the cone portion 405 of a given shell 130 accommodates a working distance for a portion of the corresponding tip 120. Sometimes, a cone can be used with a universal length that would provide ideal signals from a wide range of tooth surfaces.
    [064] In one embodiment, a calibration device is additionally provided for use in calibrating the handpiece response. In the example implementation shown in Figure 9, the calibration device 500 includes an internal axial bore 510 adapted to receive the outer surface of the tip portion 120. The calibration device 500 includes a calibration reference material 520, such as a material hydroxyapatite suitable for the calibration of a photothermal and / or luminescence signal. A second calibration device that houses a blackbody reference material, such as glassy carbon, can also be provided.
    [065] Referring again to the example device shown in Figure 9, the calibration reference material 520 is housed within the calibration device 500 in such a way that, when the calibration device is attached to the tip portion 120, the calibration reference material 520 is located in or near the focal element of the focusing element 240, thus facilitating the collection of a reference signal when a measurement is taken. The calibration device can be produced from machined plastic, so that it does not scratch the outer surface of the tip portion 120 when in use, and is manufactured with sufficient tolerance for the correct alignment of the tip with the calibration reference material. In one example, the calibration reference material 520 is housed in a separate portion 530 which is removably attached to the main body of the calibration reference device 500 for removal and / or replacement. In order to ensure placement of the calibration reference device 500 in a suitable position on the tip portion 120, the positioning mechanism such as a spring plunger 540 that presses a small notch into the tip portion 120 or tension structure can be added to the main body.
    [066] Although the modalities presented are related to applications involving oral health diagnosis, it must be understood that the scope of the present disclosure is not limited to dental uses and applications. The device disclosed here can be used for a wide range of applications, in addition to dental detection, including other biological detection and diagnosis applications, and non-destructive testing of various materials.
    [067] The specific modalities described above have been shown by way of example, and it should be understood that these modalities may be susceptible to various modifications and alternative forms. It should also be understood that the claims should not be limited to the particular forms disclosed, but should instead cover all modifications, equivalents and alternatives that fall in the spirit and scope of this disclosure.
    权利要求:
    Claims (15)
    [0001]
    1. An apparatus for detecting photothermal radiation from an object, said apparatus comprising: an elongated housing comprising a portion of the portable proximal body (110) connected to a portion of the thermally conductive distal tip (120); a laser (205) for producing a laser beam within said housing; a focusing element (240) positioned to focus said laser beam through an opening within said distal portion of the tip of said housing and on a surface of said object, and collecting photothermal radiation generated within said object in response to said beam laser, in which said focus element is configured to collect said luminescence radiation, in addition to said photothermal radiation; a dichroic beam separator (220) positioned within said housing to spatially separate said photothermal radiation from said laser beam; and an infrared detector (260) provided within said housing to detect said photothermal radiation; an optical filter (245) positioned to transmit said sampled luminescence radiation and to reject the scattered energy of the laser; a photodetector (250) positioned to detect said sampled luminescence radiation; an optical sampling element (230) provided within said housing, wherein said optical sampling element is positioned to redirect the sampled luminescence radiation; wherein at least said laser beam and said infrared detector are provided on a thermally conductive optical bench; characterized by the fact that said thermally conductive optical bench is housed within said proximal body portion and connected to a proximal end of said thermally conductive distal tip portion, such that said optical bench is supported within said portion body by said distal tip portion, and such that said distal tip portion provides a heat sink for the heat generated by optical components connected to said optical bench.
    [0002]
    Apparatus according to claim 1, characterized by the fact that said optical sampling element (230) is a detector prism.
    [0003]
    Apparatus according to claim 1 or 2, characterized by the fact that said dichroic beam separator (220) is configured to reflect said laser beam and transmit said photothermal radiation; and wherein said dichroic beam separator is additionally configured to reflect luminescent radiation that is generated within said object and collected by said focusing element (240).
    [0004]
    4. Apparatus according to claim 1 or 2, characterized in that said dichroic beam separator (220) is configured to transmit said laser beam and reflect said photothermal radiation.
    [0005]
    Apparatus according to any one of claims 1 to 4, characterized in that it additionally comprises an optical absorbent element in such a way that said photothermal radiation encounters said optical absorbent element before said infrared detector (260), and in that said optical absorbent element is configured to transmit said photothermal radiation and absorb residual laser energy.
    [0006]
    Apparatus according to claim 6, characterized in that said optical absorbing element is additionally configured to absorb residual luminescent radiation that is generated within said object and collected by said focusing element (240).
    [0007]
    Apparatus according to any one of claims 1 to 6, characterized in that said distal portion (120) of said housing additionally comprises a reflective element (235) for externally redirecting said laser beam along a direction that it is substantially orthogonal to a propagation axis of said laser beam within said housing.
    [0008]
    Apparatus according to any one of claims 1 to 7, characterized in that said distal portion of the tip (120) of said housing comprises a camera (300) for forming the image of said object.
    [0009]
    Apparatus according to claim 8, characterized by the fact that said opening is a first opening and in which said camera is configured to form an image of said object through a second opening that is adjacent to said first opening.
    [0010]
    Apparatus according to any one of claims 1 to 9, characterized in that it additionally comprises a shell (130) which is removably attachable to said distal portion of the tip (120) of said housing, wherein said shell comprises an opening, and wherein said opening is aligned with said opening when said shell is attached to said housing.
    [0011]
    Apparatus according to claim 10, characterized by the fact that said shell (130) additionally comprises a conical projection, and in which said opening is positioned at a distal end of said conical projection; wherein a distance between said aperture and said focusing element (240) is approximately equal to a working distance of said focusing element.
    [0012]
    Apparatus according to claim 10 or 11, characterized by the fact that it additionally comprises a cover material provided between said shell (130) and said distal tip portion (120) of said housing, wherein said housing material cover is at least partially transparent to said laser beam and said photothermal radiation.
    [0013]
    Apparatus according to any one of claims 1 to 12, characterized by the fact that it additionally comprises a calibration device (500) removably attachable to said distal portion of the tip of said housing (120), wherein said device of The calibration comprises a calibration reference material, wherein said calibration reference material (520) is positioned within said calibration device in such a way that said laser beam is directed towards said calibration reference material when said calibration device is attached to said housing.
    [0014]
    14. System, characterized by the fact that it comprises: said apparatus, as defined in any one of claims 1 to 13; and a control and processing unit (1) connected to said apparatus; wherein said control and processing unit is configured to supply power to said device and to process signals detected by said device.
    [0015]
    15. System according to claim 14, characterized in that said control and processing unit (1) comprises a phase-sensitive detection system for detecting a signal related to said photothermal radiation in response to a modulation of said laser beam.
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    法律状态:
    2018-12-26| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2019-08-13| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2020-04-07| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2020-10-27| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 13/05/2011, OBSERVADAS AS CONDICOES LEGAIS. |
    2022-03-08| B21F| Lapse acc. art. 78, item iv - on non-payment of the annual fees in time|Free format text: REFERENTE A 11A ANUIDADE. |
    优先权:
    申请号 | 申请日 | 专利标题
    US33443610P| true| 2010-05-13|2010-05-13|
    US61/334436|2010-05-13|
    PCT/CA2011/050303|WO2011140664A2|2010-05-13|2011-05-13|Handpiece with integrated optical system for photothermal radiometry and luminescence measurements|
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