EP1915102A2 - Outils pour realiser et preparer un perçage pour des implants dentaires et implant dentaire correspondant - Google Patents

Outils pour realiser et preparer un perçage pour des implants dentaires et implant dentaire correspondant

Info

Publication number
EP1915102A2
EP1915102A2 EP06776688A EP06776688A EP1915102A2 EP 1915102 A2 EP1915102 A2 EP 1915102A2 EP 06776688 A EP06776688 A EP 06776688A EP 06776688 A EP06776688 A EP 06776688A EP 1915102 A2 EP1915102 A2 EP 1915102A2
Authority
EP
European Patent Office
Prior art keywords
thread
section
dental implant
drill
conical
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP06776688A
Other languages
German (de)
English (en)
Inventor
Roland Streckbein
Stephan Meyer
Martin Ellerhorst
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
STRECKBEIN, ROLAND
Original Assignee
Bego Implant Systems & Co GmbH
Bego Implant Systems & Co KG GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Bego Implant Systems & Co GmbH, Bego Implant Systems & Co KG GmbH filed Critical Bego Implant Systems & Co GmbH
Publication of EP1915102A2 publication Critical patent/EP1915102A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0089—Implanting tools or instruments
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
    • A61C8/0022—Self-screwing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
    • A61C8/0022—Self-screwing
    • A61C8/0025—Self-screwing with multiple threads
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
    • A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
    • A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
    • A61C8/0069—Connecting devices for joining an upper structure with an implant member, e.g. spacers tapered or conical connection
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
    • A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
    • A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
    • A61C8/0054—Connecting devices for joining an upper structure with an implant member, e.g. spacers having a cylindrical implant connecting part

Definitions

  • the present invention relates to tools for the preparation and preparation of bores for the anchoring of dental implants and a corresponding dental implant.
  • the present invention relates to a drill for making a bore in jawbone for the anchoring of dental implants, consisting of a shank and a conical cutting part.
  • a drill for making a bore in jawbone for the anchoring of dental implants, consisting of a shank and a conical cutting part.
  • the present invention relates to a thread former for producing a thread in a bore of a jaw bone for anchoring dental implants, in particular in a bore made with a drill according to the present invention, although it would also be possible in principle, the thread former according to the invention in one to use with other drilling tools, but in the result identically produced bore.
  • the present invention also relates to a dental implant, which consists of a threaded part and a second, a tooth crown-bearing part, which are connected to each other by means of a clamping screw, wherein the Threaded portion is matched to the thread produced in the thread of the present invention in the bore of the jawbone.
  • a dental implant which is suitable for anchoring in a hole in a jawbone, with
  • the first lower portion is provided with an external thread having a first pitch
  • the second upper portion is provided with an external thread having a second pitch smaller than the first pitch
  • a transition section is arranged in which a thread is formed whose geometry changes continuously following the first section from the geometry of the first thread for connection to the second section in the geometry of the thread of the second section ,
  • the dental implant developed in this way is based on the knowledge that, in order to achieve satisfactory primary stability and to enable rapid and reliable healing, it is advantageous if an external thread is provided on the dental implant both in the cancellous bone and in the anchoring region in the cortical bone.
  • the external thread must be adapted to the specific properties of the surrounding tissue and this is inventively achieved in that the external thread for the cancellous region has a greater slope than the external thread for the cortical region.
  • a smooth area can be provided or partially a thread and partially a smooth surface can be formed here.
  • the transition between the two external thread regions is continuous, ie a transition region is arranged between the two external thread regions, in which the pitch of the external thread changes continuously, that is to say without steps.
  • the outer thread geometry of the first lower section is assumed at the border adjacent to the first lower section, and this geometry is continuously changed so far that the outer thread geometry of the second upper section is up to the border adjacent to the second upper section of the dental implant Section is reached.
  • the invention achieves the advantage that when screwing in the dental implant according to the invention a targeted displacement of bone tissue takes place, which causes a desired compression of the bone tissue around the implant and thus positively influence the Primmaschinestabili- and the healing.
  • the dental implant can be further developed by the first lower portion is conically tapered downwards.
  • Such a conical design also causes a favorable displacement of bone tissue when screwing the dental implant according to the invention and can thus also achieve a favorable compression of the bone tissue to the dental implant.
  • the conical taper is achieved by the core diameter of the thread tapers conically from top to bottom and the outer diameter of the thread is cylindrical.
  • the thread depth of the dental implant in the first lower portion is thus reduced towards the top by the core diameter increasing from bottom to top with the outside diameter of the thread remaining the same.
  • This embodiment causes compression of the surrounding bone tissue by displacement with the core of the thread.
  • the increased thread depth in the tip region of the dental implant thus formed can be used for a particularly favorable connection in cancellous bone, which likewise typically has a low density in the depth of the jaw bone than in the edge region of the jaw bone.
  • the conical taper can also be achieved by the outer diameter of the thread tapers conically from top to bottom and the core diameter is cylindrical.
  • the core of the thread does not cause a progressive displacement, but this displacement is achieved by the threaded threads, which conically widen from bottom to top with respect to their outside diameter. The thread depth of this embodiment thus increases from the lower tip to the top.
  • the conical taper can be achieved by tapering the outer diameter and the core diameter of the thread from top to bottom.
  • the displacement and compression of the bone tissue during screwing takes place both by the core area of the thread as well as the flanks of the thread.
  • the embodiment makes it possible to keep the thread depth constant over the entire first lower portion by making the conical taper of the outer diameter and the core diameter at a coincident angle.
  • the thread depth may also decrease or increase, as viewed from the lower tip of the dental implant, by making the conical taper of the outer diameter smaller or larger than that of the core diameter.
  • the core diameter and / or the outer diameter of the thread in the second upper portion is cylindrical.
  • This geometric design of the second upper portion of the dental implant is advantageous for a damage-free and firm anchoring of the dental implant in the cortical region and also allows a good seal of the dental implant against the oral cavity by a firm attachment of oral mucosa and cortical bone to the implant.
  • the cylindrical configuration as explained above with respect to the first lower section, can be effected by a cylindrical geometry of the core diameter or a cylindrical geometry of the outer diameter, wherein correspondingly the outer diameter or core diameter are each not cylindrical, for example convex or otherwise shaped can. It is particularly preferred, however, to form both the core diameter and the outer diameter of the thread in the second upper section cylindrical.
  • the above-mentioned object is achieved in that the drill is designed as a stepped drill by the cutting part consists of a first conical front portion and an adjoining, also conical base portion, wherein the drill diameter graded at the transition from the front portion to the base portion. tig extended by an amount that is between 10% and 25% of the diameter of the front section immediately before the transition to the base section.
  • the bore conical is known in principle.
  • a conical stepped bore is produced, wherein the (near the jaw bone) near-surface base portion due to the step-like enlargement produces an average 10-25% larger, but slightly conical bore, while the subsequent, deeper introduced into the jaw bone section of the bore has a correspondingly smaller diameter with an overall conical shape.
  • the front portion has expediently a length between 5 and 15 mm and the base portion has a length of at least 1, 5 mm, preferably of about 3 mm.
  • the diameter of the enlarged bore portion which covers the jawbone area close to the surface, ie the corticalis of the jawbone is about 5%.
  • both the thread former and the corresponding implant do not have a step-shaped taper corresponding to the drill, but rather have a uniformly conically tapering course, the cone angle typically being on the order of 4 ° to 5 ° and conveniently located somewhere in the Range can be between 2 ° and 10 °.
  • the bore is thus made such that the widened portion has an enlarged portion from the bone surface directed to the row of teeth, initially over a depth of typically between 1, 5 and 3 mm, and subsequently at a depth which may comprise a further 5-15 mm. is rejuvenated accordingly.
  • a thread former is introduced, which is equipped with a similar cone angle as the drill, but has no stepped taper or extension, however, which is dimensioned so that the diameter of the enlarged portion after screwing into the bore by about 5% is increased, so the diameter of the deeper hole section is widened by an amount between 15 and 30%.
  • the thread former is deliberately not designed as a tap, but, as the name implies, as a tool forming the thread, namely by plastic deformation of the bone material.
  • the thread former also has no cutting lugs or the like, as otherwise known from thread cutting tools, but only a corresponding thread, which preferably has low friction relative to the bone material and as a screw is screwed into the pilot hole, wherein the bone material through the corresponding threads pushed outward and compressed.
  • the basic conical shape distributes the thread forming process over several turns of the thread former. Because of the mentioned differences in diameter, the area of the cancellous bone is deformed and compressed much more strongly than the area of the corticalis. This also corresponds to the very different strengths of corticalis and cancellous bone.
  • a further aspect of the invention is a thread former for producing a thread in a bore of a jawbone for anchoring dental implants, which is fashioned such that the thread former has a first lower conical section with an external thread and an adjoining second upper cylindrical section having an external thread, and the thread in the second section has the same pitch as the thread in the first section.
  • This thread former according to the invention is particularly suitable for the preparation of the cavity for insertion of a previously described dental implant.
  • the thread of the thread former preferably has the larger thread pitch of the first lower portion of the dental implant, so that the thread former produces an internally threaded cavity in which the threads of the lower first portion of the dental implant come to lie exactly congruent and two threads of the upper part of the dental implant come to lie in a thread of the formed thread.
  • the thread former has a first front section and a second section connected thereto, the first section having a length of between 5 and 15 mm and the second section having a length of at least 1.5 mm, and wherein the second portion has a finer thread compared to the first portion.
  • both the extended pilot hole and the second portion of the thread former are conical, so that the first threads of the thread provided in the second section may not initially or only slightly with the upper edge of the extended Contact hole.
  • a significant engagement of the upper, second threaded portion of the thread former takes place, depending on the configuration, under certain circumstances only during the last 1 -1, 5 mm of the helical feed movement of the thread former.
  • the thread of the second portion of the thread former is a fine thread and the thread of the first, front portion of the thread forming a coarse thread, which also creates a deeper thread profile, additional tensioning forces can occur during further screwing the thread former, which the Ewear - Making the thread former difficult and to a certain extent also lead to a slight deformation of the coarse thread lying further inside the bone and the fine thread lying in the area of the corticalis.
  • the pitches of the coarse and fine threads do not differ, or at least do not differ too much, even if in extreme cases differences in the slopes of up to 50% are possible, if the fine-thread section is relatively late, ie for example engages only in the wall of the extended bore section during the last revolution of the thread former. It is more expedient, however, to reduce the difference in the pitch or to bring the gradients closer together, so that the pitch of the fine thread is at least 60%, preferably 80 or 90%, of the coarse thread.
  • the fine thread may in a preferred variant also identically have the same pitch as the coarse thread, wherein the fine thread property, namely a larger number of threads per axial unit length can be achieved simply by the fact that the fine thread of the upper threaded portion is made more smoothly, so for exampleteil warmth or dreiwill while the coarse thread of the first, front portion is formed only catchy.
  • the fine thread could be made with a separate thread former or the fine thread portion of the thread former could be rotatable relative to the coarse thread portion to adjust the number of revolutions or threading speed between coarse and fine threads according to the different pitches ,
  • the fine thread has a twofold to threefold finer structure and is accordingly also produced with a smaller tread depth, which is also appropriate for the firmer material of the corticalis.
  • the thread former is preferably made of stainless steel and has a low surface roughness of less than 5 ⁇ . This ensures that when forming the thread only a slight friction occurs and the bone material effectively displaced and is not or only slightly removed. It is even better if the surface roughness is less than 5 ⁇ and particularly preferred is an embodiment in which the stainless steel material of the thread former has a surface roughness of less than 1 ⁇ is polished. In particular, thread formers with electropolished surface and a surface roughness of well below 1 ⁇ , for example, 0.4 ⁇ , have proven to be well suited.
  • the surface roughness is the spatial mean value of the amount of deviations of the surface from an average surface.
  • the thread of the thread former also has additional special features.
  • the profile of the coarse thread of the first section and possibly also the profile of the fine thread of the second section is asymmetrically similar to a sawtooth profile, with an upwardly or outwardly facing flank, which forms a smaller angle with the axis of the thread former than the second flank of the Thread profile, which lies on the other side of the thread ridge or on the other side connects to the first edge and which includes a relatively larger angle with the axis of the thread former.
  • the smaller angle of the first flank to the axis of the thread former is of the order of 30 ° and is in any case less than 40 °, while the angle which the second flank encloses with the axis of the thread former is greater than 60 ° and, for example, approximately 70 to 80 ° or even more.
  • This second flank is directed toward the interior of the jaw bone with a corresponding implant, while the first flank is directed outwards toward the tooth side.
  • teeth are primarily subjected to pressure during use, in which case the second flanks, which are much stronger for the axis of the drill, absorb this pressure load and transmit it to the jawbone.
  • the lower tensile loads can be readily absorbed by the flanks enclosing the axis of the thread former and allow a better elastic catching of the occurring forces.
  • the two extending between two thread ridges flanks of the thread are otherwise connected to each other via a curved portion with alternating radii of curvature.
  • the first flank section (associated with FIG the axis of the thread includes the smaller angle) first a radius ⁇ , while at the other edge portion a radius r 2 connects, which is smaller than the radius ⁇ .
  • These two radii are in turn connected to each other by a transition radius r 3 , which is greater than each of the radii r t , r 2 and preferably also greater than the sum of these two angles.
  • the radius T 1 lies in the range between 0.2 and 0.3 mm, the radius r 2 between 0.1 and 0.2 mm, and the radius r 3 between 0.35 and 0.7 mm.
  • the corresponding implant has - apart from special cases to be discussed - a thread identical to the thread, wherein only the axial length of the fine thread section can differ in the implant from the axial length of the corresponding fine thread of the thread former, since the thread forming possibly different deep fine thread according to the respective depth of the enlarged bore portion, while the implant or the threaded portion of the implant is adapted to a specific application in which a certain, fixed depth of the extended bore portion is present, which was then equipped with the fine thread.
  • the implant is, as already mentioned, formed in two parts and consists of a threaded part which is screwed into the threaded bore produced in the jaw bone, and an anchored thereto, a tooth crown-bearing part.
  • the connection is usually made by a clamping screw which is screwed into an internal thread, which is provided in a recess of the threaded part of the implant.
  • This recess extends from the outwardly facing end face of the threaded portion inwardly and is also stepped, with only the more inner portion has a matching internal thread for the clamping screw while the adjoining and extending to the end face of the threaded portion in contrast something expands is and expediently has a hexagonal or octagonal profile, which acts as anti-rotation.
  • Other cross sections that can act as anti-rotation come into consideration.
  • a tooth crown-carrying part of the implant has a corresponding counterpart to the recess formed as a rotation and is inserted into this, wherein additionally a clamping screw extends through a central bore of the second part through into the internal thread of the recess of the threaded part and screwed is, wherein a head of this screw is supported on the surrounding the central bore edge of the second part of the dental implant.
  • the threaded portion and the head of the clamping screw connecting shaft portion has a smaller diameter than corresponds to the core of the thread of the clamping screw.
  • a non-threaded shank portion of a tightening screw has a diameter that approximately corresponds to the outer diameter of the threaded portion, namely, because corresponding threads are usually inserted into a cylindrical shank, i. be pressed or screwed.
  • the shaft of the clamping screw has a 10-30% smaller diameter than corresponds to the core of the thread.
  • a clamping screw with an M2 thread is used, in which the diameter of the shaft connecting the threaded portion and the head is only about 1.6 mm.
  • transitions of this shaft to both the head and the threaded portion of the clamping screw has a radius of at least 0.1 mm, preferably of about 0.2 mm. It has been shown that a clamping screw formed in this way is better secured against unintentional loosening and holds the two parts of the implant together permanently securely.
  • the thread former if the fine thread section is designed to be more continuous, but has the same thread pitch as the coarse thread section, which is designed to be single or has fewer threads than the fine thread section.
  • the fine thread may also have a smaller pitch than the coarse thread. Due to the conical shape of the threaded hole, the fine thread section of the threaded part of the implant is only relatively late, e.g. only during the last millimeter of axial movement, with the fine thread engaged.
  • the fine thread sooner engages the bore wall and, depending on the selected cone angle and the tread depth of the thread, already engages the upper edge of the enlarged bore. Therefore, to form the thread fine thread and coarse thread should have the same slope, otherwise one or both threads would be too deformed and possibly completely destroyed.
  • FIG. 1 shows a two-part dental implant in a longitudinal section with a clamping screw connecting the two parts
  • FIG. 2 shows an external view of the threaded part 10 of the implant according to FIG. 1
  • FIG. 3 shows the threaded part 10 of the implant according to FIG. 1, partly in axial section
  • FIG. 4 shows the thread of the threaded part 10 corresponding to the circle 4 in FIG. 2,
  • FIG. 5 shows an end view of the threaded part 10 from above
  • FIG. 6 shows a side view of a clamping screw
  • FIG. 8a-c show a view of a second embodiment of a dental implant according to the invention in side view (a), longitudinally cut side view (b) and top view from above (c),
  • Figure 9a-c is a view of a third embodiment of a dental implant according to the invention in side view (a), longitudinal sectional side view (b) and top view from above (c), and
  • FIG. 10 shows a section of the thread of the dental implant or thread former in the lower section.
  • FIG. 1 shows a two-part implant according to the invention with a threaded part 10, a tooth crown-carrying part 20 and a clamping screw 30 connecting the two parts 10, 20.
  • the second tooth crown-carrying part 20 of the implant is hollow throughout and has a central bore , the tapering stepwise in the lower region, wherein the lower end of the second part 20 terminates in a securing pin 31, which has an octagonal outer profile and sits in a corresponding, octagonal receptacle 4 of the threaded part 10.
  • the second part 20 still has a dental crown holder 32.
  • the threaded part 10 will be described later in detail.
  • the part 10 has a central blind bore, which is widened in the upper region (axial length e) 1 to an octagonal receiving profile 4 for the securing pin 31 and which is provided with an internal thread 11 in the lower section (axial length c) , In the preferred embodiment, this is a metric thread with a nominal diameter of 2 mm.
  • the screw 30 consists of a screw head 31, a shaft 32 and a threaded portion 33. The screw 30, as well as the threaded portion 10, in connection with the other figures will be described in detail.
  • FIG. 2 shows only the threaded part 10 in a side view.
  • the threaded portion 10 has a slightly conical shape, wherein the cone angle of the corresponding enveloping conical surface, ie the opening angle of diametrically opposite sides of the cone, about 5 °, but could also be chosen slightly smaller or larger.
  • the threaded portion, generally designated 10, consists of a lower threaded portion 1 which extends over an axial length a, including a threadless tip portion 8, and an upper fine thread portion 2 having an axial length b (see Figure 3).
  • the upper edge of the fine thread section 2 terminates approximately flush with the surface of a jaw bone, while the section 1 is completely received in the interior of the jaw bone and extends in particular in the cancellous bone of the jaw bone, while the fine thread section 2 substantially to the denser and harder outer wall of the bone, the so-called corticalis, is limited.
  • the lower threaded portion 1 has a coarse thread with a thread height H, while the upper fine thread section 2 has only one thread height h, however, is designed as a double-threaded thread, with the result that in each case a gear has twice the value of the pitch h, the axial Distance between two successive threads shows, however, parallel to each other in the Fine thread section rotate.
  • the value h is still approximately half of the value H in the case of a double-threaded thread the pitch of the fine thread can be approximated in the section 1 despite the greater number of individual threads per axial unit length of the pitch of the coarse thread.
  • the lower tip 8 of the threaded part 10 which is formed as a cone with a cone angle of about 90 °, an axial length s, which is typically of the order of 1 mm or slightly smaller.
  • top and bottom are used in the context of the present description according to the orientation of the parts in the figures. It is understood, however, that the position of these parts in the jaw of a patient of course deviates from this orientation, it being further clear that the
  • Tip 8 is always located inside the jaw bone, while the upper edge of the fine thread section 2 substantially with the surface of the jaw bone, in which the corresponding bore is introduced, completes.
  • the blind hole consisting of the octagon receiver 4 and the female threaded portion 3, which is provided for the connection to the upper part 20 of the implant, which carries a corresponding tooth crown, can be seen more precisely.
  • the introduced centrally into the upper portion of the threaded portion 10 hole in the upper part is extended to an octagonal profile, the octagonal shape of the profile is best seen in the plan view of Figure 5.
  • This octagonal cavity 4 in the profile serves as a receptacle and against rotation for a corresponding octagonal pin 21 of the upper implant part 20.
  • This receiving bore tapers in the further course downwards to a threaded bore 3 which in the preferred embodiment has an M2 internal thread - has.
  • the cavity 4 with the octagonal profile has an axial length e and the adjoining cavity, which has the internal thread 3, has an axial length c.
  • the length e is typically in the order of 1, 5-2 mm and c in the order of 2-4 mm.
  • FIG. 4 shows a section of the thread profile of the external thread of the lower section 1 of the threaded part 10.
  • the thread has a sawtooth profile with a first flank 6, which is flatter towards the axis, and a second flank 7, which is more inclined towards the axis has the edge 7 down, ie towards the interior of the jawbone, while the flank 6 points upwards towards the row of teeth.
  • the two flanks 6 and 7 are interconnected by a curved surface with three different radii, the relationship is r 2 ⁇ T 1 ⁇ r 3 and wherein the portion with the radius T 1 adjoins the flank 6, the surface with the radius r 2 connects to the flank 7 and the surface with the radius r 3 connects the surfaces curved with ⁇ and r 2 .
  • Figure 5 is a top plan view of threaded portion 10 of the implant, so that you can see relatively well in this view, the internal thread 3 or its inner diameter and the octagonal profile 4.
  • the octagonal profile typically has a clear dimension of about 2.5 mm, with the overall diameter D of the upper portion 2 of the threaded portion 10 typically being between 3.5 and 4.5 mm.
  • FIGS 5 and 6 show the clamping screw 3 used for the connection of the two implant parts.
  • the clamping screw 3 has, as already mentioned, a head 31, which is supported on a shoulder inside the bore of the upper implant part 20, which is at the transition is formed from the upper shaft portion of the implant part 20 to the plug 21 acting as anti-rotation.
  • the clamping screw also has a lower threaded portion 33, and a threaded portion 33 and the head 31 connecting shaft 32.
  • the screw 30 has a length which is typically in one Range of about 7-12 mm, of which a good quarter on the head 31 and the threaded portion 33 accounts and almost half of the shaft 32.
  • the shaft 32 is formed with a significantly smaller diameter than the threaded portion 33, wherein the diameter di the shaft is only about two-thirds of the nominal diameter d 2 of the threaded portion 32.
  • the head 31 in turn has an even larger diameter d 3 , which is again 10-15% greater than the diameter of the threaded portion 33, which is necessary only because the threaded portion 30 through the central bore of the upper implant part and into the threaded bore of the lower implant part 10 must be introduced while the head must be supported simultaneously on the edge of the step-like tapered bore of the upper implant part 20.
  • the head 31 is also provided with a hexagon socket 34 into which a suitable hex key can be inserted to rotate the screw.
  • the hexagon socket 34 is clearly visible especially in the plan view of the screw head from above according to FIG.
  • the threaded portion 30 has an M2 thread, with the shank 32 only having a diameter in the range between 1.3 and 1.6 mm. This is between 30 and 20% below the nominal diameter of the threaded portion 33.
  • the implant according to the invention proves to be more durable and better resilient than previous implants and has relatively short healing times. It is understood, however, that the foregoing description has given only a preferred embodiment, while the specific embodiments may be varied within the scope of the independent claims.
  • a second embodiment of the dental implant according to the invention has a lower section 110, in which the dental implant has an external thread with an anchor for anchoring in the spon- gi Hampshire bone adapted thread pitch and thread depth is provided. Both the outer diameter and the core diameter of this external thread tapers conically towards the tip 109 of the dental implant. The tip 109 of the dental implant is also conically tapered at a steeper angle and flattened on the underside 108. A recess 107, which extends from the flat 108 in a lower portion of the threaded portion 1 10, provides a self-tapping effect of the dental implant in this diameter range.
  • a transition section 120 adjoins the lower threaded section 110.
  • the thread pitch and thread depth are continuously reduced to thread pitch and thread depth, which is advantageous for the attachment of denser cancellous bone or cortical bone.
  • This thread pitch and thread depth is continued in a head section 130 of the implant which continues further upwards to the transition region.
  • the thread depth in the head portion of the implant is about one third of the thread depth in the lower threaded portion 110.
  • the thread pitch in the head portion 130 is half the thread pitch in the lower portion 110.
  • Both the core diameter and the outer diameter of the thread in the head portion is in the axial direction kon- constantly, ie the envelope is cylindrical.
  • a cylindrical, outwardly smooth head section region 140 is arranged on this embodiment of the dental implant, which is bounded at the top by an axially aligned abutment surface 152.
  • the oral mucosa comes to rest after implantation, whereby, depending on skin thickness and pocket depth, parts of it can also lie in the region of the thread in the head section.
  • a tool engagement is integrally formed, which is provided by an external hex 150.
  • the edges 151 of the external hexagon are tapered upwards. new, so that the application of a tool during the implantation process is facilitated.
  • the implant terminates with a head termination surface 154 into which a blind bore is made along the central axis of the implant.
  • the blind hole comprises, starting from the head end surface 154 a chamfer 161, to which a cylindrical portion 162 connects.
  • An internal thread 163 with a corresponding tool outlet 164 adjoins the cylindrical section 162.
  • the internal thread 163 serves to screw in a screw of the type described above, in order to connect the dental implant according to the figures 8a-c with a tooth structure part, thereby forming a two-part dental implant.
  • the external hexagon 150 serves, in cooperation with an internal hexagon on the tooth structure, to prevent rotation between the mounting part and the implant part.
  • the dental implant has a tip 209, a lower section 210, a transition section 220 and a head section 230 followed by a smooth head section 240, which correspond to the corresponding sections 109-140 of the dental implant according to FIGS. 8a-c.
  • the dental implant according to FIGS. 9a-c does not have any external hexagon as tool engagement and anti-twist protection. Instead, the dental implant terminates immediately above the cylindrical smooth portion 240 with a head termination and abutment surface 252 into which a frusto-conical bore 261 is inserted.
  • the frusto-conical bore 261 opens into a hexagon socket 250 which is formed in the implant.
  • a cylindrical rischer space 253 arranged whose outer diameter is greater than the outer diameter of the hexagon socket 250.
  • the cylindrical space 253 serves as a tool outlet for the manufacture of the hexagon socket and is provided to reduce the notch effect with rounded corners.
  • an internal thread 263 with a tool outlet 264 Connected to the cylindrical space 253 downwards is an internal thread 263 with a tool outlet 264, which is analogous to the internal thread 163 and tool outlet 164 and also serves to attach a tooth structure to the dental implant according to FIGS. 9a-c, in order in this way To provide two-piece implant.
  • Figure 10 shows a section of the lower threaded portion of the thread former or dental implant in a sectional view and illustrates the thread geometry of the invention.
  • the drill axis or the longitudinal axis of the thread former or the dental implant is located.
  • the flank surface of the thread pointing obliquely upwards extends downwards in a straight thread flank section which assumes an angle ⁇ 1 to the longitudinal axis of the thread former or dental implant or drill. This angle is preferably less than 40 ° and is in particular between 25 and 30 °.
  • flank surface of the thread pointing downwards outwards extends in a straight surface section which lies at an angle ⁇ 2 to the longitudinal axis of the drill, thread former or dental implant.
  • This angle .alpha.2 is opposite to the angle .alpha.1, in the illustration according to FIG. 10 .alpha.2 is open at the bottom and .alpha.1 is open at the top.
  • the angle ⁇ 2 is in particular greater than 60 ° and is preferably about 70 °.

Landscapes

  • Health & Medical Sciences (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Dentistry (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Dental Prosthetics (AREA)
  • Dental Tools And Instruments Or Auxiliary Dental Instruments (AREA)

Abstract

L'invention concerne un foret pour réaliser un perçage dans un maxillaire en vue de l'ancrage d'un implant dentaire, ce foret comprenant une tige et une partie tranchante conique. L'invention concerne également un dispositif de formage de filet servant à réaliser un filet dans un perçage d'un maxillaire en vue de l'ancrage d'implants dentaires. Ledit perçage se présente sous la forme d'un perçage étagé généralement conique allant en diminuant d'une section de départ conique adjacente à l'ouverture du perçage à une section de fin adjacente à cette section de départ. L'invention concerne en outre un implant dentaire en deux parties, une première partie filetée (10) pouvant être vissée dans un maxillaire et une seconde partie (20) étant fixée à la première pour maintenir une couronne dentaire. L'objectif de l'invention est de créer des outils pour réaliser et préparer des perçages filetés dans des maxillaires et un implant correspondant qui permettent d'accroître la probabilité de réussite vis-à-vis de la durée de vie et de la rapidité de cicatrisation des implants. A cet effet, le foret selon l'invention se présente sous la forme d'un foret étagé dont la partie tranchante est constituée d'une première section frontale conique et d'une section de base également conique adjacente à la première section, le diamètre de ce foret au niveau de la jonction entre la section frontale et la section de base s'élargissant de façon étagée dans une proportion comprise entre 10 et 25 % du diamètre de la section frontale immédiatement avant ladite jonction. Le dispositif de formage de filet selon l'invention se caractérise en ce qu'il présente une première section avant et une seconde section adjacente à cette première section, la longueur de ladite première section étant comprise entre 5 et 15 mm et la longueur de la seconde section étant supérieure ou égale à 1,5 mm et ladite seconde section présentant un filet plus fin que celui de la première section. L'implant dentaire selon l'invention se caractérise en ce que la partie filetée (10) présente un filet à deux étages conformément au dispositif de formage de filet.
EP06776688A 2005-08-09 2006-08-08 Outils pour realiser et preparer un perçage pour des implants dentaires et implant dentaire correspondant Withdrawn EP1915102A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE200510038038 DE102005038038A1 (de) 2005-08-09 2005-08-09 Werkzeuge zum Herstellen und Vorbereiten einer Bohrung zur Aufnahme von Zahnimplantaten und entsprechendes Zahnimplantat
PCT/EP2006/007853 WO2007017257A2 (fr) 2005-08-09 2006-08-08 Outils pour realiser et preparer un perçage pour des implants dentaires et implant dentaire correspondant

Publications (1)

Publication Number Publication Date
EP1915102A2 true EP1915102A2 (fr) 2008-04-30

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Application Number Title Priority Date Filing Date
EP06776688A Withdrawn EP1915102A2 (fr) 2005-08-09 2006-08-08 Outils pour realiser et preparer un perçage pour des implants dentaires et implant dentaire correspondant

Country Status (3)

Country Link
EP (1) EP1915102A2 (fr)
DE (2) DE102005038038A1 (fr)
WO (1) WO2007017257A2 (fr)

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DE102011101253A1 (de) 2011-02-16 2012-08-16 Hager & Meisinger Gmbh Knochenschraube
JP5156113B2 (ja) * 2011-08-02 2013-03-06 株式会社松風 歯科用インプラント
EP2586398A1 (fr) * 2011-10-25 2013-05-01 Sudimplant Implant dentaire
EP2986247B1 (fr) * 2013-06-13 2019-11-13 Hager & Meisinger GmbH Implant dentaire d'un seul tenant, kit comprenant un implant dentaire et un dispositif de cintrage d'un implant
CN103550003B (zh) * 2013-11-18 2015-12-23 大连三生科技发展有限公司 易取出的种植体装置及其旋出工具
MY181111A (en) * 2014-11-27 2020-12-18 Kyocera Corp Fixture for dental implants and dental implant
US20220125556A1 (en) * 2019-03-07 2022-04-28 Tav Medical Ltd. Dental implants

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IT1237496B (it) * 1989-10-26 1993-06-08 Giuseppe Vrespa Dispositivo a vite per l'ancoraggio di protesi alle ossa, metodo per l'applicazione di tale dispositivo e relativa attrezzatura
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Also Published As

Publication number Publication date
WO2007017257A3 (fr) 2007-05-03
WO2007017257A2 (fr) 2007-02-15
DE102005038038A1 (de) 2007-02-15
DE202006020925U1 (de) 2010-12-23

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