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    • 专利摘要:
    endodontic instrument for drilling root canals of a tooth. A method for forming a dental tool or instrument having a memorized shape is described. the method comprises selecting a nitinol wire having an initial transition temperature below room temperature; milling the nitinol wire to form the dental tool or instrument to have a leg, located adjacent a first end, and a working area, with at least one cutting edge, located adjacent an oppositely conducting second end; molding the work area into a molded shape having at least one protrusion formed therein; heating the dental tool or instrument to cumulatively: a) change the initial transition temperature of the dental tool or instrument to a final transition temperature, and b) memorize the molded shape including the at least one protrusion such that the tool or instrument tooth will automatically return to the molded shape showing at least one protrusion when at a temperature at or above the final transition temperature.
    公开号:BR112018008424B1
    申请号:R112018008424-7
    申请日:2016-11-02
    公开日:2021-09-14
    发明作者:Jean-Claude Rouiller
    申请人:Fkg Dentaire S.A.；
    IPC主号:
    专利说明:

    FIELD OF INVENTION
    [0001] The present invention relates to an endodontic instrument, particularly an instrument for drilling a root canal in a patient's tooth, the instrument having a longitudinal axis and comprising a working area for forming and/or shaping and/or cutting and/or cleaning the wall of the tooth root canal, the work area being equipped with a support end piece that can be fixed in a mount. BACKGROUND OF THE INVENTION
    [0002] The cleaning and preparation of root canals of a tooth to receive filling material is achieved using drilling instruments with an active part called the working part, the purpose of which is to format and clean the root canal in preparation for receive the materials used to treat and fill the same.
    [0003] Root canals often have specific shapes with complex curves and narrow cross sections formed from constricted or oval areas that do not lend themselves to the introduction of preliminary formatting instruments. This is why instruments known as files must have characteristics that are sometimes contradictory: the files must be thin but strong, and yet flexible enough to conform to the curves of the root canal and reach the end of the canal, although, however, remaining durable enough to shape and cut the canal walls.
    [0004] These requirements oblige the dentist to carry out a process of preparatory treatment of the root canal using a wide range of tools and progressively work on adapting to the morphology of the root canal, the set of tools featuring various structures and dimensions. The intervention starts with a thin flexible instrument which will then be replaced by cross-sectional augmentation instruments until the root canal presents an internal cavity large enough to receive the filling material. This is a long and delicate series of operations, requiring attention that, for safety reasons, the treatment and filling material must completely fill the root canal and precautions taken to ensure that no residual air remains at the base of the cavity created from way to prevent any bacterial growth and possible infection.
    [0005] These instruments are difficult to introduce into the root canal. In addition, to date there is no universal instrument adapted to the morphology of the root canal to be treated that would perform all the preparatory operations in one procedure. There is a risk that instruments break, become blocked in the channel, or overheat too much, which can cause them to break. This risk is notoriously present when using mechanically actuated instruments made of nickel-titanium alloy, which wear out and must be carefully monitored by the dentist during use. There is no doubt that the use of several different instruments in succession not only increases the cost of the intervention, but also the complexity of the dentist's work and the risk to the patient.
    [0006] The US publication. No. 2010/0233648 describes a method and an endodontic instrument made of super elastic material. A rod of super elastic material is adjusted in a shaped configuration to form an instrument such that the instrument can be inserted into a root canal in a different configuration than the different shaped configuration and revert to its shaped configuration during the endodontic procedure . In order to form the rod into a desired shaped instrument, the rod is compressed (preferably ranging from about 550 MPa to about 1500 MPa) between heated forming surfaces (typically between about 100°C to about 200°C ) which causes strain on the rod.
    [0007] When the instrument is made of a flexible metallic alloy, the instrument is designed to resume its retracted shape through a mechanical action after having been used in the expanded structure format.
    [0008] A significant disadvantage of conventional root canal procedures is that a practitioner must generally use a series of endodontic files to clean and shape a diseased root canal. Typically, this series of instruments consists of a set of files of increasingly larger diameter and, as a result, an increasing taper, as the length of the working part is often kept substantially constant. Sets of such files are used to sequentially and gradually enlarge the root canal until the desired shape is achieved. Stepwise widening in relatively small increments is believed to be an important part of the conventional strategy to avoid unwanted damage and other effects to the tooth structure during the widening process, and to avoid imposing too large a torsional load. or strain on the material comprising the instrument. In this regard, a set of instruments is often used only once for a particular patient and then discarded, with each instrument in the set provided at substantial individual expense. Likewise, there is a need for an improved endodontic file design that limits the number of endodontic files needed to obtain a desired hole shape and degree of enlargement during root canal filling/therapy procedures. BRIEF DESCRIPTION OF THE DRAWINGS
    [0009] The present invention and its main advantages will become clearer from the description of the various embodiments, with reference to the attached drawings, in which: Figure 1A represents an instrument according to the invention in the format of a spade drill at the time of its introduction into the root canal of a tooth; Figures 1B to 1D represent the instrument of Figure 1A after insertion into the root canal of the tooth, with Figures 1C and 1D respectively representing cross sections in the tooth along sectional lines 1C-1C and 1D-1D, respectively; Figures 2A and 2C represent another embodiment of the instrument of the invention at the time of its introduction into the root canal of a tooth, with Figure 2C representing a cross section in the tooth root along sectional line 2C-2C; Figures 2B and 2D represent the instrument of Figure 2A after the introduction of the root canal of a tooth, with Figure 2D depicting a cross section in the root along the sectional line 2D-2D; Figures 3A and 3C represent another variation of an expandable instrument according to the invention in a first operating state at the root of a tooth, with Figure 3C depicting a section through the root along axis 3C-3C; Figures 3B and 3D represent the instrument called the expandable instrument in Figure 3A in a second operating state, with Figure 3D depicting a cut through the treated root of the tooth along the 3D-3D axis; Figures 4A and 4B depict an expandable instrument similar to Figures 3A to 3D in a different working configuration at the root of a tooth, with Figure 4B depicting a cut through the root along axis 4B-4B; Figure 5A illustrates a variation of the instrument of the invention called a tubular instrument inserted into the root of a tooth, but in the non-operational position; Figure 5B is an enlarged end view of the working area of the instrument of Figure 5A in the non-operating position; Figure 6A illustrates the instrument of Figures 5A and 5B in the operating position within the tooth root; Figure 6B is an enlarged end view of the working area of the instrument of Figure 5A in the operating position; Figure 7 is a diagrammatic view of a nitinol wire for use in the manufacture of a dental tool or instrument in accordance with the present invention; Figure 8 is a diagrammatic view of a first milled portion of the nitinol wire which forms a working area of the dental tool or instrument; Figure 8A is an enlarged diagrammatic view of the ground nitinol wire of Figure 8, after attachment of the conventional drive coupled to its rod, while Figure 8B is an enlarged diagrammatic partial section of area 8B of Figure 8A; Figure 9 is a diagrammatic view of a washed and electro-polished dental tool or instrument in accordance with the present invention; Figure 10 diagrammatically shows a two-part mold for molding a desired memorized shape into a dental tool or instrument; Figure 11 diagrammatically shows a mold in two parts, in its closed position, conforming with the tool or dental instrument in the desired shape to be memorized and heated in an oven; Figure 12 diagrammatically shows a two-part mold being rapidly cooled; Figure 13 diagrammatically shows the opening of the mold in two parts, after its rapid cooling, for removal of the tool or dental instrument with the memorized format; Figure 14 diagrammatically shows the dental tool or instrument with the memorized format; Figure 14A diagrammatically shows the straightening of the tool or dental instrument in Figure 14, after its cooling to a temperature below its transition temperature; Figure 14B diagrammatically shows the partial removal of the straightened tool or dental instrument from Figure 14, after its adequate cooling for its martensitic phase; Figure 15 diagrammatically shows the dental tool or instrument, with the memorized format, contained inside a protective case; Figure 16 diagrammatically shows a typical process for attaching a dental tool or instrument to a rotating tool; Figure 16A diagrammatically shows the dental tool or instrument attached to a rotating tool while the dental tool or instrument is still contained within the protective case; Figure 16B diagrammatically shows the dental tool or instrument, fixed to a rotating tool, after the partial removal of the dental tool or instrument from the protective case; Figure 16C diagrammatically shows the adjustment of the adjustable depth indicator together with the tool or dental instrument, once the tool or dental instrument is partially removed from the protective case; Figure 16D diagrammatically shows the straightened tool or dental instrument, in its martensitic phase and fixed to the rotating tool, completely removed from the protective case and ready for insertion into a root canal; Figure 17 diagrammatically shows the dental tool or instrument in its martensitic phase immediately at the entrance to a root canal just before the dental tool or instrument reaches its transition temperature; Figure 18 diagrammatically shows the dental tool or instrument, according to the present invention, operating within an upper region of a typical root canal after transitioning to its austenitic phase and returning to its memorized format; Figure 19 diagrammatically shows the volume/circumscribed radius increased by at least one bend, undulation, curvature, discontinuity, protrusion or protrusion formed in the working area of the tool or dental instrument during its rotation; Figure 20 diagrammatically shows the dental tool or instrument, in accordance with the present invention, operating within a central region of a typical root canal; Figure 21 diagrammatically shows the dental tool or instrument, in accordance with the present invention, operating within a lower region of a typical root canal; Figure 21A is a diagrammatic cross-sectional view, along sectional line 21A-21A, of the root canal shown in Figure 21; and Figure 21B is a diagrammatic cross-sectional view, along sectional line 21B-21B, of the root canal shown in Figure 21. DETAILED DESCRIPTION OF THE ACHIEVEMENT
    [0010] The instrument represented by Figures 1A to 1D is a manual type of instrument designed to be attached to the end of a handle that allows the practitioner to scrape the inwardly facing surface of the generally oval root canal of a patient's tooth essentially using movements forward and backward and pivoting movements around the longitudinal axis A of the instrument. The instrument (10) comprises a working area (11) made of metallic wire comprising one or more wires extending into a support end piece (13) held by an assembly (14), in this case a cable enabling the professional to manipulate the instrument. Figure 1A represents the instrument (10) in the position of insertion into the root canal (21) of a tooth (20). In this position, the work area (11) of the instrument (10) is in what is called the retracted position, in this case generally straight, which facilitates its introduction into the root canal (21) and allows it to easily pass through the narrowing ( 16) visible on the channel. At room temperature, the work area (11) maintains its generally straight, retracted configuration, considering that the metallic alloy it is made of presents a property known as "shape memory". This quality, known in itself, allows a suitable metal alloy to present a first geometric shape at a given temperature range and assume a different geometric shape after moving to another temperature. In this case, the working area (11) of the instrument, made of a nickel-titanium-based alloy, is generally straight at room temperature, for example, from 0 to 35°C, preferably between 10 and 30°C and especially on the order of 20°C, and assumes an expanded structure configuration at a higher temperature. At a “low” temperature, the material is in its so-called “martensitic” phase and its shape is relatively flexible and malleable, which facilitates the introduction of the instrument into the root canal. At a higher temperature, the material enters a phase known as “austenitic” and the instrument assumes a structured configuration that allows it to conform to the channel walls, regardless of the channel shape. In order to return the material from its martensitic phase to its austenitic phase, depending on the materials, a first temperature variation is applied, such that an elevation located within a temperature range of 0° to 60°C and preferably of 25° to 40°C. in order to return the material from its austenitic phase to its martensitic phase, depending on the materials, a second temperature variation is applied, in such a way as to reduce the temperature to a value called the transformation value, situated within a range of temperatures extending from 60° to 0°C and preferably 40°C and 25°C for certain nickel alloys.
    [0011] Alloys that are useful for their memory properties are mainly copper-zinc-aluminum-nickel, copper-aluminum-nickel and zinc-copper-gold-iron alloys. Obviously other alloys with similar properties can be used.
    [0012] The temperature rise can be accelerated by using heating means incorporated in the base instrument or by using external means such as, for example, sodium hypochlorite (NaOCl) which is used to disinfect the root canal. This compound can be injected through a warming syringe currently used by professionals in the field.
    [0013] The expanded structure format assumed by the work area (11) of the instrument (10) is shown in Figures 1B to 1D. The work area (11) in this exemplary embodiment takes the form of a flat drill essentially filling the entire space of the root canal (21) as shown in Figures 1C and 1D. The drill is extremely flexible in such a way that it adapts to the internal shape and contour of the root canal (21). In the narrow part (16) of the channel, loops (17) on the drill are less pronounced than in the enlarged sectors (18) and (19) corresponding to the bottom and entrance of the channel (21) respectively.
    [0014] Figures 2A to 2D represent an instrument (10) according to the invention, of the mechanically driven type, coupled in one of the channels (21) of a molar tooth (20) with two root canals. In Figures 2A to 2C, the work area (11), in its retracted configuration, is generally straight, allowing easy introduction into the root canal (21). In Figures 2B and 2D, the work area (11) assumed its expanded structure configuration after an increase in temperature resulting from either contact with the patient's body or with a heating resistor (not shown) present in the assembly (14) that supports the instrument (10). In the example shown, the instrument is mechanically rotated and when in a structured state, it is formatted as a corkscrew. The working area (11) on the instrument (10) is also of sufficiently flexible consistency that the cross section can adapt to the cross section of the root canal (21) which is more or less conical. For this reason, the work area (11) is made of a metallic alloy wire with a shape memory that assumes its configuration in an expanded structure after a rise in temperature or a change in temperature. The wire may be generally circular or perhaps angular in its cross section such that the instrument functions as a smoothing, cutting or abrading tool depending on the desired result. The professional can use several instruments with different or complementary functions depending on the initial shape of the root canal to be treated.
    [0015] Figures 3A to 3D represent another embodiment of an instrument according to the invention of the mechanically actuated type. This instrument (10), called an expandable instrument, has specific characteristics allowing it to adapt to the shape and dimensions of a root canal or “machine” the canal to give it the desired shape and dimensions for the subsequent treatment of the root canal. The instrument (10), in the state shown in Figures 3A and 3C, is introduced into one of the root canals (21) on the tooth (20). This channel comprises a slight bulge (21a) in its central part, followed by a narrowing (21b). The working area (11) on the instrument (10) adapts to this configuration. As the instrument illustrated in Figures 2A to 2D, this instrument is mechanically rotated by its assembly (14) and depending on the cross section of the metallic wire that constitutes it, its action produces either machining, cutting, abrading or smoothing the walls of the root canal ( 21). In the present case, the aim is to increase the upper part of the channel while eliminating the narrow part (21b) so as to facilitate the introduction of the filling substance. To do this, the instrument (10) expands, takes the form of a corkscrew with a generally circular cross section, and acts on the walls by cutting or eroding the tooth body material, as shown in Figures 3B and 3D.
    [0016] In the realization shown in Figures 4A and 4B, the expansion of the instrument (10) occurs essentially at the top (30) of the work area (11) and the objective is to shape the root canal (21) into a cone. The working area (11) can be one of cutting, abrading or smoothing depending on which shape is contemplated for the channel (21).
    [0017] Figures 5A and 5B illustrate another embodiment of the instrument (10) whose working area (11) is generally tubular and has a twisted appearance. The lower end (12) of this work area (11) is axially divided by a certain length and comprises two sectors (12a) and (12b) which are visible in Figure 5B. When the working area (whose end (12) is enlarged in Figure 5B) is in the non-operating position, the two sectors (12a) and (12b) are juxtaposed at the axial extent of the rest of the working area (11). The introduction of the instrument's working area (10) into the root canal (21) is easy given its straight tubular configuration. In this working position shown in Figures 6A and 6B, the lower end (12) was opened after a rise in temperature due to the shape memory properties of the alloy that makes up the instrument (10), and the two sectors (12a) and (12b) form an angle to each other that describes a more or less open cone when the tool is rotated by its rotating assembly (14). The dentist's object is to create an enlarged cavity (22) at the end of the root canal (21), the cavity being intended to receive the filling paste and prevent the entrapment of air microbubbles in the base of the canal. Air microbubbles actually contain oxygen which can feed bacteria and cause decay, producing a more or less long-term infection.
    Turning now to Figures 7-21B, a further embodiment of the present invention will now be described. As this embodiment is very similar to the previously discussed embodiments, only the differences between this new embodiment and the previous embodiment will be discussed in detail while identical elements will receive identical numerical references.
    [0019] According to this embodiment, the dental tool or instrument (10) according to the present invention is manufactured from a nitinol wire (32) (e.g. typically with about 56% nickel and about 44% titanium by weight). This nitinol wire (32) is in an austenitic phase at room temperature (about 72 degrees Fahrenheit or about 22 degrees Celsius) in order to be able to machine the nitinol wire (32) into the desired tool or dental instrument, see Figure 7. That is, when the nitinol wire (32) is at a temperature below the transition temperature, the nitinol wire is in its martensitic phase in which the nitinol wire (32) is normally flexible, malleable and/or temporarily deformable into a desired shape, for example, it can be manipulated into a desired curved shape or some other desired shape or shape. However, once the nitinol wire (32) has reached a temperature at or above the transition temperature, for example typically well below room temperature in this case, the nitinol wire (32) naturally and automatically returns to its austenitic phase. that the nitinol wire (32) becomes more rigid and naturally returns to its initial manufacturing configuration or shape, which is typically a linear shape or configuration, as shown generically in Figure 7. In the austenitic phase of the nitinol wire (32 ), the nitinol wire (32) always adopts its linear manufacturing configuration or shape which is particularly well suited and beneficial for the machining/milling/conversion of the nitinol wire (32) into a dental tool or instrument (10), such as it is conventional in the art.
    [0020] According to the present invention, the dental tool or instrument (10) is first manufactured by selecting a nitinol floss (32) suitable for the manufacture of the dental tool or instrument (10). Since the dental tool or instrument (10) will be used in a patient's mouth, it is desirable for a final transition temperature of the nitinol wire (32), and for the resulting dental tool or instrument (10), to be slightly below body temperature ie about 90.5 + 4 degrees Fahrenheit (ie 32.5 + 3 degrees Celsius). However, it should be noted that for other applications, a nitinol wire (32) having a different transition temperature, for example, or greater or less than about 90.5 + 4 degrees Fahrenheit (ie, 32.5 + 3 degrees Celsius), can be used without departing from the spirit and scope of the present invention.
    [0021] As in the conventional technique, the selected nitinol wire (32), which is manufactured in a conventional manner, normally presents conventional super elastic properties. That is, the nitinol wire (32) has either the martensitic phase, in which the nitinol wire (32) is generally malleable or temporarily deformable into a desired configuration or shape as long as the nitinol wire (32) remains at a temperature below its initial transition temperature of the nitinol wire (32), as an austenitic phase, in which the nitinol wire (32) will automatically return to its originally manufactured configuration or shape, for example, which is typically its configuration or shape originally manufactured linear, as soon as the temperature of the nitinol wire (32) reaches or exceeds the initial transition temperature of the nitinol wire (32).
    [0022] In accordance with the present invention, as discussed in more detail below, the resulting dental tool or instrument (10) will exhibit a final transition temperature slightly below body temperature, i.e., about 90.5 + 4 degrees Fahrenheit (ie. is, 32.5 + 3 degrees Celsius). However, during the manufacturing process of the nitinol wire (32) it is desirable for the nitinol wire (32) to have an initial transition temperature that is typically well below room temperature. This ensures that the nitinol wire (32) is in its austenitic phase, i.e. relatively firm at room temperature, which helps with the machining/grinding/conversion of the nitinol wire (32) at room temperature in a tool or dental instrument (10).
    [0023] After selecting a nitinol wire (32) suitable for the manufacture of the dental tool or instrument (10), the nitinol wire (32) is then subjected to a grinding or cutting operation (Figures 8 and 8A ) in which at least one, and possibly two or more longitudinal or elongated cutting surfaces or edges (34), e.g. helical cutting surfaces or edges, are cut or otherwise formed along a longitudinal length or axis That of just a part of the nitinol wire (32), for example, typically in a helical shape. Such first milled portion of the nitinol wire (32) generally forms a working area (11) of the dental tool or instrument (10), as generally shown in Figure 8. A second opposite end portion of the nitinol wire (32) substantially remains. unground or unaltered and thus forms a leg (38) of the dental tool or instrument (10). The unground opposite end of the dental tool or instrument (10) forms a leg (38) which assists in coupling the dental tool or instrument (10) during use.
    [0024] Upon completion of the grinding process, the tool or dental instrument (10) is then cut to the desired length. Subsequently, as shown in Figure 8A, a conventional drive coupling (55), which facilitates the coupling and attachment of the dental tool or instrument (10) by a conventional rotary tool (59), is conventionally attached to the leg ( 38) of the dental tool or instrument (10).
    [0025] It is important to note that the formation of the working area (11) is done purely by a milling, cutting or other similar machining operation. In the past, helical cutting surfaces have been introduced to the wire (32) by applying twisting motions under certain conditions, for example, applying extreme pressures and low temperatures. However, such twisting movements introduced unwanted stress and tended to cause unwanted fatigue in the nitinol wire (32) and should therefore be avoided. It should be noted that stress and fatigue tend to cause the dental tool or instrument (10) to break after a limited amount of rotations and/or bending. That is, breakage tends to occur after only a nominal load is repeatedly applied and then removed when the level of maximum cyclic stress applied was much lower than the actual tensile strength, and in fact, much lower than the stresses produced so much. the martensitic phase and the austenitic phase of the instrument or tool (10). For this reason, prior art yarns tend to break prematurely and thus are generally suitable for a single application only.
    [0026] After the formation of at least one, and possibly two or more longitudinal or elongated surfaces or cutting edges (34) along the working area (11) of the dental tool or instrument (10) and attachment of the drive coupling (55), the dental tool or instrument (10) [and then subjected to washing and an electro-polishing process. During this washing and electropolishing process, a very thin layer or part (35), for example, possibly 0.01-0.03 mm (see Figure 8B), from the outer surface of the tool or dental instrument (10), is removed. Such removal of a very thin layer or part (35) from the outer surface of the dental tool or instrument (10), by the electro-polishing process, tends to remove or, at the very least, smooth the contour of any very small cracks or other imperfections or deformations (33), which may have formed on the external surface of the dental tool or instrument (10) during the grinding process, and such electro-polishing process makes the dental tool or instrument (10) more resistant to breakage and/or fatigue during use.
    [0027] As a result of the above process, the dental tool or instrument (10) is designed in such a way that the dental tool or instrument (10) can be rotated at a rotation speed of about 900 + 100 rpms while performing a root canal procedure, for a time duration of at least a few minutes, without fracture and/or breakage, thus extending and prolonging the life of the tool or dental instrument (10) and minimizing the possibility of the tool or instrument dental (10) inadvertently breaks or fractures during use, possibly leaving a broken or fractured portion of the dental tool or instrument (10) in the root canal.
    [0028] After the process of washing and electropolishing and cutting to the desired length of the dental tool or instrument (10), the dental tool or instrument (10) is then ready to present both: a) its changed initial transition temperature to its final transition temperature such that the transition temperature of the dental tool or instrument (10) will be about or slightly below body temperature, and b) hot molded to memorize a desired shape or configuration that features at least one bend , undulation, curvature, discontinuity, bulge or protrusion (36) formed within and along the working area (11) of the dental tool or instrument (10). As shown in Figure 14, the at least one protrusion (36) is formed only along a portion of the working area (11), typically located at or adjacent to the free tip of the dental tool or instrument (10) and spaced apart and spaced apart. of the leg (38). Typically, at least one protrusion (36) is formed closer to the free tip of the dental tool or instrument (10) than to the leg (38) of the dental tool or instrument (10). The at least one protrusion (36) and the leg (38) of the dental tool or instrument (10) both define and lie in a single plane. In addition, preferably the dental tool or instrument (10) is not twisted when being placed within the mold (42) so as to reduce the stress induced on the dental tool or instrument (10).
    [0029] The at least one protrusion (36) generally has a curved or arcuate shape having a length of about 1 and 16 mm (measured along a longitudinal axis A of the dental tool or instrument (10)) and a width W (measured with respect to the longitudinal axis A of the dental tool or instrument (10)) from about 0.1 to about 3.0 mm or so. It should be noted that the overall shape of the at least one protrusion (36) to be memorized by the working area (11) of the dental tool or instrument (10) may vary, depending on the particular application, without departing from the spirit and scope of this invention. The important aspect of the at least one protrusion (36) is that, by rotating the dental tool or instrument (10), the at least one protrusion (36) increases the radius and/or volume circumscribed by the dental tool or instrument (10) as the dental tool or instrument (10) rotates. This increased radius and/or volume of the dental tool or instrument (10) facilitates a more complete scraping and removal of pulp from the inwardly facing surfaces of a root canal, especially for the complex and narrow curved sections of the root canal that are not normally required. lend themselves to complete pulp removal. In addition, in accordance with the present invention, if desired, two or more sequential protrusions (36) can be formed in the work area, one sequentially after the other (not shown), depending on the particular application.
    [0030] As indicated above, it is highly desirable that the dental tool or instrument (10) is in the austenite stage, at room temperature, during the manufacturing process. That is, as long as the dental tool or instrument (10) is at a temperature above its initial transition temperature, for example, typically a temperature of about 50 + 10 degrees Fahrenheit (10 + 5 degrees Celsius) in this case, the dental tool or instrument (10) is not malleable or temporarily deformable. As such, the working area (11) of the dental tool or instrument (10) does not conform or is readily molded into a desired shape, i.e., the shape of the at least one desired protrusion (36).
    [0031] The initial transition temperature of the dental tool or instrument (10) is changed, according to the present invention, by placing the dental tool or instrument (10) in a mold (40) and by applying only a minimum pressure , for example, the weight of a mold top, heating tool or dental instrument (10) to a desired temperature for a desired period of time. As generally shown in Figure 10, the base mold (42) has a cavity (46) formed therein that includes a negative imprint (48) of the at least one protrusion (36). Each cavity (46) of the mold (40) is sized and shaped to receive and accommodate a dental tool or instrument (10) and mold the working area (11) of the dental tool or instrument (10) into the at least one protrusion (36 ) desired. When the dental tool or instrument (10) is initially placed within the cavity (46) of the base mold (42), the working area (11) of the dental tool or instrument (10), as the tool or instrument dental (10) is still currently in its austenitic phase, does not follow or conform to the contour of the negative impression (48) that is formed on the base mold (42) and is the desired shape to be obtained at the end of the final product of the dental tool or instrument (10).
    [0032] In order to force the tool or dental instrument (10), still in its austenitic phase, to closely follow and conform to the contour of the at least one protrusion (36) formed in the base mold (42) an upper mold of complement (44) is coupled to the base mold (42) so as to captively accommodate the dental tool or instrument (10) within the cavity (46) of the mold (40). As indicated above, the upper mold (44) has a combined positive impression (50) which corresponds to the negative impression (48) of the at least one protrusion (36) to be formed in the working area (11) of the dental tool or instrument ( 10). Likewise, according to the upper mold (44), with the positive impression (50) of the at least one protrusion (36), it combines with the base mold (42), the working area (11) of the tool or instrument dental (10) is forced or induced to adopt, conform and closely follow the contour of the combined negative and positive impressions (48, 50) of the base mold (42) which is the desired configuration or shape to be obtained and memorized by the end product of the dental tool or instrument (10), as generally shown in Figure 14. It should be noted that the upper mold (44) applies only minimal pressure, eg typically significantly less than a thousand pounds per square inch, more preferably less of a hundred pounds per square inch, and the most preferred being less than ten pounds per square inch or so, in order to completely avoid any compression of the dental tool or instrument (10). That is, the negative imprint (48) and the combined positive imprint (50) of the at least one protrusion (36) are shaped. Size and/or diameter at least as large as the shape, size and/or outside diameters of the working area of the dental tool or instrument (10) (preferably without clearance) such that the present invention merely reconfigures the dental tool or instrument (10) into a desired new shape of the tool or dental instrument (10) to be memorized, but does not physically change the size/diameter of the tool or dental instrument (10). Typically the minimum force required to reconfigure or realign the dental tool or instrument (10) into a new desired shape to be memorized, and subsequently heated in the mold (40), is less than a hundred pounds per square inch, more preferably less of ten pounds per square inch, and the most preferred being less than a few pounds per square inch. Such minimal force on the working area (11) occurs without causing any permanent deformation (that is, any deformation that is not reversible only by changing the temperature) of the tool or dental instrument (10). This minimal force merely facilitates reconfiguration or alignment and keeps the dental tool or instrument (10) in a new memorized format such that, after the heating and cooling processes discussed above, the dental tool or instrument (10) will memorize this new format in which the newly memorized super elastic configuration of the dental tool or instrument (10) features a linear leg (38) and a non-linear work area (11), as shown generally in Figure 14.
    [0033] When combining the top and base molds (44, 42) together, only a minimal amount of force or pressure is required and this minimizes possible metal fatigue. Furthermore, no compression of the dental tool or instrument (10) takes place. Thereafter, the mold (40), with the one or more dental tools or instruments (10) accommodated, is then heated to a desired temperature by a conventional heater (45). The heat supplied to the dental tool or instrument (10) is designed to both: a) change the initial transition temperature of the resulting dental tool or instrument (10) to a final transition temperature, and b) permanently “remember” the molded shape of the at least one protrusion (36) formed in the mold (40), as generally shown in Figure 11, for example.
    [0034] As a result of this process, once the dental tool or instrument (10) has been heated for a sufficient period of time in the mold (40) and then subsequently cooled, as described in more detail below, the dental tool or instrument (10) remembers the shape of the combined negative and positive impressions (48, 50) of the at least one protrusion (36) formed in the mold (40). In addition, due to this heating process for a sufficient period of time in the mold (40), the initial transition temperature of the dental tool or instrument (10) is changed from its initial transition temperature of about 50 + 10 degrees Fahrenheit (10 + 5 degrees Celsius) for your final transition temperature which is slightly below body temperature, ie about 90.5 + 4 degrees Fahrenheit (ie 32.5 + 3 degrees Celsius). As a result, thereafter each time the temperature of the dental tool or instrument (10) is at or above the final transition temperature of the dental tool or instrument (10), i.e. any time the dental tool or instrument (10 ) is in its austenitic phase, the dental tool or instrument (10) will always automatically return to this memorized molded shape of at least one protrusion (36) that mirrors the combined negative and positive impressions (48, 50) of the mold (40) .
    [0035] During the heating process, the dental tool or instrument (10) is heated to a sufficient temperature that a) facilitates the memorization of the molded shape of the dental tool or instrument (10), and b) also facilitates changing the temperature of initial transition of the tool or dental instrument (10) to a new final transition temperature. That is, the heating temperature of the dental tool or instrument (10), which facilitates both changing the original transition temperature and memorizing the molded shape, is typically a temperature of between 392 and 707 degrees Fahrenheit (200 and 375 degrees Celsius) for a time period of between 30 minutes and 240 minutes. More preferably, the heating temperature of the dental tool or instrument (10), which facilitates both changing the original transition temperature to a new final transition temperature and memorization of the molded shape, is a temperature of between 482 and 662 degrees Fahrenheit (250 and 350 degrees Celsius), and more preferably, the heating temperature of the tool or dental instrument (10), to facilitate both changing the transition temperature and memorizing the molded shape, is a temperature of about 572 degrees Fahrenheit ( 300 degrees Celsius). More preferably, the heating time of the dental tool or instrument (10), to facilitate both changing the original transition temperature to a new final transition temperature and memorizing the molded shape, is a duration of between 45 and 90 minutes.
    [0036] While the dental tool or instrument (10) is accommodated within the mold (40) and heated to the desired memory temperature for the desired period of time, the dental tool or instrument (10) is generally tempered in order to change its shape original memorized to a new memorized format that the dental tool or instrument (10) will always automatically adopt and return each time the dental tool or instrument (10) is at or above the new final transition temperature, i.e., when the dental tool or instrument (10) is in its austenitic phase. That is, the dental tool or instrument (10) memorizes and automatically adopts this newly memorized format such logo and each time the dental tool or instrument (10) goes through a transition from its martensitic phase to its austenitic phase.
    [0037] After heating the dental tool or instrument (10), inside the mold (40) to the desired temperature for the desired period of time, the mold (40) and the dental tool or instrument (10) are then quickly cooled, that is, cooled in a liquid bath (52) (eg, cold water, for example), as generally shown in Figure 12. Such rapid cooling of the tool or dental instrument (10) assists with annealing the tool or dental instrument ( 10) and memorizes the shape of the at least one protrusion (36).
    [0038] After cooling, the second upper mold (44) is separated from the base mold (42) in order to open the mold (40) and allow the removal of the tool(s) or dental instrument(s) (is) (10), as shown generally in Figure 13. As a result of the above process, a) the original transition temperature of the dental tool or instrument (10) is changed to a final transition temperature that is slightly below the body temperature , that is, about 90.5 + 4 degrees Fahrenheit (ie 32.5 + 3 degrees Celsius), and b) the dental tool or instrument (10) remembers its molded shape from at least one protrusion (36) and adopts this memorized format as soon and every time the dental tool or instrument (10) stops, it transitions from its martensitic phase to its austenitic phase. It should be noted that when the dental tool or instrument (10) is at a temperature below its final transition temperature, the dental tool or instrument (10) is in the martensitic phase and is bendable or flexible.
    [0039] However, this memorized format, in the form of at least one protrusion (36), can make the packaging, storage and/or transport of the tool or dental instrument (10) a little difficult. In order to solve this problem, after manufacture, the dental tool or instrument (10) can be sufficiently cooled by spraying the dental tool or instrument (10) with a cooling/sanitizing liquid or gas, as generally shown in Figure 14, in order to sanitize and bring the dental tool or instrument (10) to a temperature below its final transition temperature, for example, in such a way that the dental tool or instrument (10) is in its martensitic phase at room temperature. Subsequently, the at least one protrusion (36) of the dental tool or instrument (10) can then be manually straightened (as generally shown in Figure 14A) which aids in the insertion of the dental tool or instrument (10) or its removal from the package. suitable, such as a protective cover or protective case (54), as generally shown in Figure 14B.
    [0040] As indicated above, in order to ensure the protection of the dental tool or instrument (10), the dental tool or instrument (10), after its manufacture and sterilization, is packed in the cover or protective case (54). The protective case (54) is typically a thin hollow case that receives and accommodates at least the working area (11) of the dental tool or instrument (10), and at least a portion of the leg (38), within a internal cylindrical compartment of this, while the drive coupling (55) of the tool or dental instrument (10) remains located outside the protective case (54) and exposed to the external environment. That is, the drive coupling (55) remains readily accessible for engagement with the rotary tool (59) in a conventional manner. This aids in the easy attachment of the drive coupling (55) of the dental tool or instrument (10) to the desired rotating tool (59). Finally, the dental tool or instrument (10), accommodated within the protective case (54), is packaged within a conventional protective packaging that maintains the sterility of the dental tool or instrument (10), until the use of the dental tool or instrument (10) if desired.
    [0041] The protective case (54) is preferably at least partially transparent such that the dental tool or instrument (10) is at least partially visible through the protective case (54). The protective case (54) is open at its first open end and completely closed at its second closed end. An outer surface of the protective case (54) is provided with a measuring scale (56), which starts with an initial measurement indication, eg 0.0 cm, at the first open end (60) of the protective case (54), typically ends with a final measurement indication, for example 25 cm, adjacent to its second closed end. The leg (38) of the dental tool or instrument (10) supports an adjustable depth gauge (58). The adjustable depth indicator (58) is slid along the dental tool or instrument (10), by an endodontist prior to use, so as to indicate a desired insertion depth of the working end of the dental tool or instrument (10) in the desired root canal.
    [0042] Once the endodontist has determined the root canal depth of the patient's tooth to be treated, the endodontist attaches the drive coupling (55) to a suitable conventional rotary tool (59) (see Figures 16 and 16A) to drive the dental tool or instrument (10), during use, at a desired rotational speed, eg 900 + 100 rpm. Once the exposed end of the drive coupling (55) is securely attached to the rotary tool (59), the endodontist can then partially remove the dental tool or instrument (10) from the protective case (54), a sufficient distance until a part of the working area (11) of the dental tool or instrument (10), still remaining inside the protective case (54), is equal to the predetermined depth of the root canal of the tooth of the patient to be treated (Figure 16B). Next, the adjustable depth indicator (58) is then slid by the endodontist along the dental tool or instrument (10) from the leg (38) towards the opposite working area (11) until the indicator adjustable depth (58) rests against the first open end (60) of the protective case (54) (Figure 16C). As a result of such a process, the adjustable depth indicator (58) now provides a visual indication to the endodontist, as soon as the adjustable depth indicator (58) is located closely adjacent to/supports the tooth of the patient to be treated, that the dental tool or instrument (10) is fully inserted into the root canal and should not be inserted deeper into the root canal. That is, the adjustable depth indicator (58) functions as an interruption indicator for the endodontist during the use of the dental tool or instrument (10).
    [0043] Prior to complete removal of the dental tool or instrument (10) from the protective case (54), the dental tool or instrument (10) is typically cooled, for example, sprayed with a conventional compressed gas or coolant such as compressed air (not shown). The compressed coolant gas or liquid gradually cools the protective case (54) and such cooling of the protective case (54), in turn, sufficiently cools at least the working area (11) of the dental tool or instrument (10) to a temperature below its final transition temperature such that the working area (11) of the dental tool or instrument (10) can then be temporarily manipulated, molded or shaped or to a generally linear configuration, to a slightly curved configuration, to a folded configuration or some other desired shape or configuration. For example, the rotary tool (59) can be operated to rotate the dental tool or instrument (10), as the dental tool or instrument (10) is being cooled and located inside and by the protective case (54) of so as to allow the temporary deformation of the working area (11) of the dental tool or instrument (10) to the desired linear shape or configuration, for example a linear shape as shown in Figure 16D. Such desired configuration or shape, for example, linear, curved or bent configuration, generally facilitates insertion of the leading end of the dental tool or instrument (10), by the endodontist, into an entry opening of the root canal of the tooth to be treated, such as generically shown in Figure 17.
    [0044] It should be noted, however, that as soon as the dental tool or instrument (10) is heated by the tooth, which is typically at body temperature, the dental tool or instrument (10) instantly and automatically undergoes a phase transition martensitic to its austenitic phase, as shown in Figure 18, and the dental tool or instrument (10) simultaneously adopts and conforms back to its memorized shape from the at least one protrusion (36). It should be noted that the memorized shape is a little more rigid than the flexible martensitic phase, and is therefore more effective in scraping or removing the pulp from the surface facing the inside of the root canal of the tooth to be treated, as generically shown in Figures 20, 21, 21A and 21B. The at least one protrusion (36) of the dental tool or instrument (10) is highly effective in removing, cleaning and clearing the pulp from tubular or cylindrical areas and regions of the root canal, as well as oval and other areas and regions non-cylindrical root canal, which normally do not lend themselves to complete cleaning and pulp removal by dental tools available in the current state of the art.
    [0045] According to the present invention, the at least one protrusion (36) of the dental tool or instrument (10), when rotated by the rotating tool (59), increases the radius and volume (61) (Figure 19) enclosed and/or circumscribed by the dental tool or instrument (10).
    [0046] It should be noted that if the dental tool or instrument (10) merely had a linear shape or configuration, the radius or volume (61) circumscribed by the dental tool or instrument (10), when in its austenitic phase, would be merely equal to the volume defined by the dental tool or instrument (10), as generally shown in Figure 17. As is clear from this Figure, it is quite difficult for the endodontist to manipulate the dental tool or instrument (10) in order to completely clean and remove all the pulp from the inwardly facing surfaces of the root canal, especially in the areas of narrow, curved cross-sections of the root canal, which typically do not lend themselves to complete removal and cleaning of the pulp.
    [0047] Due to the increased radius and volume of at least one protrusion (36) of the dental tool or instrument (10), as the dental tool or instrument (10) is rotated by the rotating tool (59), the surface(s)( s) or cutting edge(s) (34) of the at least one protrusion (36) is brought into intimate contact with and scrapes against the inwardly facing surface of the root canal, especially in areas with complex and narrow curved cross sections of the root canal. root canal that typically do not lend themselves to complete pulp removal and cleaning. That is, the memorized shape of the at least one protrusion (36) assists in keeping the surface(s) or cutting edge(s) (34) in constant and intimate contact with the inwardly facing surface of the root canal during the use. Such constant and intimate contact with the inwardly facing surface of the root canal occurs continuously throughout the time the dental tool or instrument (10) is located within the root canal, for example, constantly as the endodontist gently introduces the tool or dental instrument (10) towards and away from the bottom of the root canal. Increasing the radius and volume of the at least one protrusion (36) of the dental tool or instrument (10) as it is rotated within the root canal, in association with the back and forth introduction movement of the endodontist, ensures the entire removal of all the pulp contained within the root canal being treated.
    [0048] Preferably, the nitinol wire, for use with the present invention, includes 54-57% by weight nickel and 43-46% by weight titanium.
    [0049] After the complete removal of the dental tool or instrument (10) from the root canal, the dental tool or instrument (10) can either be properly discarded or can possibly be cooled, for example, sprayed with a compressed gas or coolant conventional sanitized. The sanitized compressed gas or coolant cools at least the working area (11) of the dental tool or instrument (10) to a temperature below its final transition temperature. Similar to when first formed, the working area (11) of the dental tool or instrument (10) may then be temporarily manipulated, molded or shaped or into a generally linear configuration, a slightly curved configuration, a bent configuration or some other shape or form. desired configuration. Such manipulation generally facilitates insertion of the leading end of the dental tool or instrument (10) by the endodontist into an inlet opening of a sanitized protective case (54). The dental tool or instrument (10) can then be stored in its martensitic phase until desired for future use.
    [0050] The present invention is not limited to the described embodiments, but may be subject to different modifications or variations. In particular, despite the fact that the variations described are triggered manually and mechanically, it is also possible to use ultrasonic vibrations to control the instrument (10). Additionally, depending on the shapes selected, the root canal preparation may vary. These variations can also be obtained by adaptations in the shape of the metallic wire from which the instrument (10) is made, the shape possibly being smooth or rough, round or angular, etc.
    权利要求:
    Claims (15)
    [0001]
    1. Method for the formation of a dental tool or instrument (10) having a memorized format, characterized by the fact that it comprises: the selection of a nitinol wire having an initial transition temperature of 50 ± 10 degrees Fahrenheit (ie, from 10 ± 5 degrees Celsius); milling the nitinol wire (32) at room temperature to form the dental tool or instrument (10) to have a leg (38), located adjacent a first end, and a work area (11), with pile. at one cutting surface, located adjacent a second, opposite conductive end, the nitinol wire (32) is in the austenitic phase during milling; molding the work area (11) into a molded shape having at least one protrusion (36) in a mold (40) by applying a pressure of less than 1000 pounds per square inch on the work area (11) which is just sufficient for inducing the working area (11) of the dental tool or instrument (10) to follow a contour of the at least one protrusion (36) of the mold (40), and without causing any permanent deformation of the dental tool or instrument (10); heating the tool or dental instrument (10) accommodated in the mold (40) to a temperature between 200 and 375 degrees Celsius for a period of time between 30 and 240 minutes to: a) change the initial transition temperature of the tool or dental instrument (10) for a final transition temperature of 90.5 + 4 degrees Fahrenheit (ie, 32.5 + 3 degrees Celsius); and at the same time, b) memorizing the molded shape including the at least one protrusion (36) such that the dental tool or instrument (10) will automatically return to the molded shape having the at least one protrusion (36) as soon as the dental tool or instrument (10) is at a temperature equal to or greater than the final transition temperature.
    [0002]
    2. Method according to claim 1, characterized in that it further comprises: heating the dental tool or instrument (10) to a temperature between about 482 and 662 degrees Fahrenheit (250 and 350 degrees Celsius) to change the temperature of initial transition of the tool or dental instrument (10) and at the same time memorize the molded shape presenting at least one protrusion (36) for a time period of between 30 minutes and 240 minutes.
    [0003]
    3. Method according to claim 1, characterized in that it further comprises: heating the tool or dental instrument (10), for a time between 30 minutes and 240 minutes, to a temperature that changes the initial transition temperature of the tool or dental instrument (10) for the final transition temperature and at the same time facilitates the memorization of the molded shape presenting at least one protrusion (36) , when the dental tool or instrument (10) is at a temperature equal to or greater than the temperature. of final transition.
    [0004]
    4. Method according to claim 1, characterized in that it further comprises: heating the tool or dental instrument (10), for a period of time between 45 minutes and 90 minutes, to a temperature that changes the initial transition temperature of the dental tool or instrument (10) to the final transition temperature and at the same time facilitates the memorization of the molded shape having at least one protrusion (36) when the dental tool or instrument (10) is at a temperature equal to or higher at the final transition temperature.
    [0005]
    5. Method according to claim 1, characterized in that it further comprises: the formation of at least one protrusion (36) to present a curved shape and an arcuate shape that increases at least one between the radius and a volume of the tool or dental instrument (10) when rotated by a rotating tool (59) with the at least one protrusion (36) and the dental tool or instrument (10) defining a plane.
    [0006]
    6. Method according to claim 1, characterized in that it further comprises: the formation of at least one protrusion (36) to present a curved length or an arcuate length between 1 and 16 mm and a width, measured in relation to a length of the tool or dental instrument (10), from 0.1 to 3.0 mm, without twisting the tool or dental instrument (10).
    [0007]
    7. Method according to claim 1, characterized in that it further comprises: the memorization of the molded shape presenting the at least one protrusion (36) by placing the mold of the tool or dental instrument in the mold (40) presenting both a negative impression (48) as a positive impression (50) of the at least one protrusion (36) to be formed on the at least one working area (11) of the dental tool or instrument (10); applying, by means of the mold (40), a pressure of less than one thousand pounds per square inch to the working area (11) of the dental tool or instrument (10); and heating the dental tool or instrument (10) to a temperature of between about 392 and 707 degrees Fahrenheit (200 and 375 degrees Celsius) for a period of time of between 30 minutes and 240 minutes in order to 1) change the temperature from the initial transition of the dental tool or instrument (10) to the final transition temperature and, at the same time, 2) memorize the molded shape having the at least one protrusion (36).
    [0008]
    8. Method according to claim 7, characterized in that it further comprises: rapid cooling of the mold (40) in order to rapidly cool the tool or dental instrument (10) after heating the tool or dental instrument (10) inside of the mold (40).
    [0009]
    9. Method according to claim 8, characterized in that it further comprises: rapid cooling of the mold by extinguishing the mold in a liquid bath in order to quickly cool the tool or dental instrument (10).
    [0010]
    10. Method according to claim 1, characterized in that it further comprises: the packaging of the dental tool or instrument (10) in a protective case (54) and an external packaging that ensures the sterility of the dental tool or instrument (10) , forming the protective case (54) to be at least partially transparent; and providing a measuring scale (56) on a surface of the protective case (54).
    [0011]
    11. Method according to claim 1, characterized in that it further comprises: the attachment of a drive coupling (55) to the leg (38) of the tool or dental instrument (10) in order to facilitate the coupling of the tool or instrument (10) to a rotary drive.
    [0012]
    12. Method according to claim 1, characterized in that it further comprises: providing an adjustable depth indicator (58) on the dental tool or instrument (10) that is slideable along the dental tool or instrument (10), prior to use, to indicate a desired depth of insertion of a working end of the dental tool or instrument (10) into a desired root canal (21).
    [0013]
    13. Method according to claim 1, characterized in that it further comprises: subjecting an external surface of the tool or dental instrument (10) to an electro-polishing process that smoothes any imperfections or deformations on the external surface of the tool or dental instrument ( 10) in order to make the dental tool or instrument (10) more resistant to breakage and/or fatigue during use.
    [0014]
    14. Method for forming a dental tool or instrument having a memorized shape, characterized by the fact that it comprises: the selection of a nitinol wire (32) having an initial transition temperature of 50 ± 10 degrees Fahrenheit (ie, from 10 ± 5 degrees Celsius); milling the nitinol wire (32) at room temperature to form the dental tool or instrument (10) so as to have a leg (38), located adjacent a first end, and a work area (11), with pile. minus one cut, located adjacent a second, opposite conductive end, the nitinol wire (32) is in the austenitic phase during milling; molding the work area (11) into a molded shape having at least one protrusion (36) in a mold (40) by applying a pressure of less than 1000 pounds per square inch on the work area (11) of the dental tool or instrument (10) which is just sufficient to induce the working area (11) of the dental tool or instrument (10) to follow a contour of the at least one protrusion (36) of the mold (40), and without causing permanent deformation of the area of work (11) of the tool or dental instrument (10); subjecting an external surface of the dental tool or instrument (10) to an electropolishing process to smooth any imperfections or deformations on the external surface of the dental tool or instrument (10) and make the dental tool or instrument (10) more resistant to breakage and /or fatigue during use; and heating the tool or dental instrument (10) accommodated in the mold (40) to a temperature between 200 and 375 degrees Celsius for a period of time between 30 and 240 minutes, as well as: a) changing the initial transition temperature of the tool or dental instrument to a final transition temperature of 90.5 ± 4 degrees Fahrenheit (ie, 32.5 + 3 degrees Celsius); and at the same time, b) memorizing the molded shape which includes a linear leg (38) and the at least one protrusion (36), such that the dental tool or instrument (10) will automatically return to the molded shape featuring the at least one protrusion (36) as soon as the dental tool or instrument (10) is at a temperature equal to or greater than the final transition temperature.
    [0015]
    15. Dental tool or instrument (10) having a memorized format, characterized in that it comprises: the dental tool or instrument (10) having a final transition temperature of about 90.5 ± 4 degrees Fahrenheit (ie, 32.5 + 3 degrees Celsius); the dental tool or instrument (10) having a leg (38) located adjacent a first end thereof and a working area (11) located adjacent an opposite second end thereof, the working area (11) consisting of a string of nitinol (32); at least one elongated cut being formed along the working area (11) of the dental tool or instrument (10); a memorized shape, having at least one protrusion (36) being formed in the working area (11) of the dental tool or instrument (10); wherein the memorized shape is formed by the simultaneous application of heat and a pressure of less than 1000 pounds per square inch to the nitinol wire (32) with an initial transition temperature of 50 + 10 degrees Fahrenheit (ie, 10 + 5 degrees Celsius) inside a mold (40); when the dental tool or instrument (10) is at a temperature below its final transition temperature, the dental tool or instrument (10) is in the martensitic phase and is moldable into a temporary shape or configuration that facilitates insertion of a conductive tip of the tool or instrument (10) into a desired root canal (21), but as soon as the dental tool or instrument (10) is at a temperature equal to or greater than the final transition temperature, the dental tool or instrument (10) automatically passes from its martensitic phase to its austenitic phase and the tool a or dental instrument (10) simultaneously adopts its memorized format presenting at least one protrusion (36), and in which at least one protrusion (36) has a curved or arcuate length between 1 and 16 mm and a width, measured in relation to a longitudinal axis of the dental tool or instrument (10), between 0.1 and 3.0 mm, the protrusion (36) is formed without torsion.
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    ES2858756T3|2021-09-30|
    US20160051339A1|2016-02-25|
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    WO2012079183A1|2012-06-21|
    CA2819204A1|2012-06-21|
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    CL2018001170A1|2018-12-14|
    SG11201803658YA|2018-05-30|
    JP2014505507A|2014-03-06|
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    法律状态:
    2020-03-10| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-07-06| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-09-14| 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 02/11/2016, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    CH02100/10A|CH704235B1|2010-12-16|2010-12-16|The endodontic instrument for root canal bore of a tooth.|
    US14/930,844|2015-11-03|
    US14/930,844|US9931179B2|2010-12-16|2015-11-03|Endodontic instrument for drilling the root canals of a tooth|
    PCT/CH2016/000140|WO2017075723A1|2015-11-03|2016-11-02|Endodontic instrument for drilling the root canals of a tooth|
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