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WO2024189100A1 - Ébauche de fraisage à composants multiples - Google Patents

Ébauche de fraisage à composants multiples Download PDF

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Publication number
WO2024189100A1
WO2024189100A1 PCT/EP2024/056705 EP2024056705W WO2024189100A1 WO 2024189100 A1 WO2024189100 A1 WO 2024189100A1 EP 2024056705 W EP2024056705 W EP 2024056705W WO 2024189100 A1 WO2024189100 A1 WO 2024189100A1
Authority
WO
WIPO (PCT)
Prior art keywords
phase
methacrylate
shore
stiff
milling blank
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.)
Pending
Application number
PCT/EP2024/056705
Other languages
English (en)
Inventor
Martin Klare
Frank Gischer
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.)
Pro3dure Medical GmbH
Original Assignee
Pro3dure Medical 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 Pro3dure Medical GmbH filed Critical Pro3dure Medical GmbH
Publication of WO2024189100A1 publication Critical patent/WO2024189100A1/fr
Anticipated expiration legal-status Critical
Pending legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/884—Preparations for artificial teeth, for filling teeth or for capping teeth comprising natural or synthetic resins
    • A61K6/887—Compounds obtained by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/0003—Making bridge-work, inlays, implants or the like
    • A61C13/0022—Blanks or green, unfinished dental restoration parts
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08F—MACROMOLECULAR COMPOUNDS OBTAINED BY REACTIONS ONLY INVOLVING CARBON-TO-CARBON UNSATURATED BONDS
    • C08F265/00—Macromolecular compounds obtained by polymerising monomers on to polymers of unsaturated monocarboxylic acids or derivatives thereof as defined in group C08F20/00
    • C08F265/04—Macromolecular compounds obtained by polymerising monomers on to polymers of unsaturated monocarboxylic acids or derivatives thereof as defined in group C08F20/00 on to polymers of esters
    • C08F265/06—Polymerisation of acrylate or methacrylate esters on to polymers thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/08—Artificial teeth; Making same
    • A61C13/087—Artificial resin teeth
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C2201/00—Material properties
    • A61C2201/007—Material properties using shape memory effect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C5/00—Filling or capping teeth
    • A61C5/007—Dental splints; teeth or jaw immobilisation devices; stabilizing retainers bonded to teeth after orthodontic treatments
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C7/00—Orthodontics, i.e. obtaining or maintaining the desired position of teeth, e.g. by straightening, evening, regulating, separating, or by correcting malocclusions
    • A61C7/08—Mouthpiece-type retainers or positioners, e.g. for both the lower and upper arch

Definitions

  • the present invention relates to a milling blank for generating a blank, typically used in the field of dental medicine.
  • dental splints such as occlusal or protrusion splints, which differ in terms of efficiency, wearing comfort and clinical indication.
  • splint materials based on PMMA are used for adjusted bite splints.
  • Dental splints of this material class comprise low deformations under pressure load (e.g. grinding) and slide more easily against each other during opposing movements of the lower and upper jaw compared to more flexible splint materials.
  • T o avoid this, the skilled person is nowadays also familiar with splint materials with a so-called thermomemory effect (insert own patent here), which are hard-flexible when inserted into the mouth, i.e. at room temperature, and whose flexibility and resilience are increased by body heat.
  • This effect also has a very advantageous effect on the wearing comfort of mucosa- supported splints compared to all the above-mentioned material classes.
  • the blank is composed of at least 2 components which differ in terms of their Shore hardnesses by at least 7 Shore D at room temperature and at least 15 Shore D at body temperature.
  • there is no further layer such as an adhesive layer, between the two material layers, i.e. incisal/occlusal material and tooth/soft tissue material.
  • an adhesive layer between the two material layers, i.e. incisal/occlusal material and tooth/soft tissue material.
  • both materials are polymerized to each other under the action of pressure and heat to create a direct chemical bonding of the two materials. This allows force peaks to be dissipated more easily, thus increasing durability and strength.
  • a first aspect of the present invention relates to a milling blank for generating a splint, wherein the milling blank comprises at least two phases, particularly a flexible phase FP and a stiff phase SP, characterised in that the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 15 Shore D higher.
  • the milling blank for generating a splint can be used to generate a dental splint.
  • the term flexible phase in the context of the specification relates to a material that has a low shore hardness.
  • the flexible phase becomes reduced its hardness and becomes more flexible at body temperature making it adjustable around the teeth, and in case of a splint is surrounding the tooth.
  • the flexible phase may comprise an internal hardness gradient with decreasing shore hardness towards the soft tissue of the jaw.
  • stiff phase in the context of the specification relates to a material with a high shore hardness.
  • the stiff phase in case of a splint is located at the occlusal plane.
  • the stiff phase may comprise an internal hardness gradient with increasing shore hardness towards the occlusal plane.
  • the term gradient in the context of the specification relates to a gradual change in shore hardness.
  • the gradient can be implemented through 3D printed layers, wherein each layer varies in their shore hardness. Through the 3D printed layers, the gradient increments can be influenced by the layer thickness. The thinner the layer, the higher the gradient, the thicker the layer, the smaller the gradient.
  • Shore hardness in the context of the specification relates to a measurement for the hardness of a material, particularly a polymer.
  • the Shore hardness is measured using a Shore durometer. High Shore values indicate a greater resistance to indentation and thus harder materials. Lower numbers indicate less resistance and softer materials.
  • the Shore A scale describes softer materials, the Shore D scale describes harder materials.
  • thermo memory effect in the context of the specification relates to a material that becomes flexible at body temperature and adapts optimally to the tooth surface and in turn becomes stiff at room temperature.
  • a first aspect of the present invention relates to a milling blank for generating a splint, wherein the milling blank comprises at least two phases, particularly a flexible phase FP and a stiff phase SP, characterised in that the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 15 Shore D higher.
  • the milling blank for generating a splint can be used to generate a dental splint.
  • the differences between the Shore Hardness is calculated between the highest part of Shore hardiness of the hard phase HP and the lowest part of the Shore hardness of the soft phase SP.
  • the flexible phase FP comprises a soft polymer A and the stiff phase SP comprises a hard polymer B.
  • the flexible phase FP consists of a soft polymer A and the stiff phase SP consists of a hard polymer B.
  • the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 18 Shore D higher, particularly the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 20 Shore D higher, more particularly the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 22 Shore D higher.
  • the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 25 shore D higher. In another particular embodiment of the first aspect of the invention, the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 30 shore D higher. In another embodiment of the first aspect of the invention, the stiff phase SP has a higher Shore hardness at body temperature than the flexible phase FP at body temperature, namely at least 15 to 30 shore D higher.
  • the flexible phase FP comprises a thermomemory effect, a temperature-dependent memory effect so that the material returns to its original shape after deformation during heating. The material becomes flexible at body temperature and adapts optimally to the tooth surface. This increases the wearing comfort of the splint and minimizes the risk of breakage.
  • the soft polymer A of the flexile phase FP and the hard polymer B of the stiff phase SP is a polymer P selected from the group consisting of polyalkyl methacrylate, polycycloalkyl methacrylate, polycycloalkyl acrylate and polyalkyl acrylate or a polymerized component of a thermoplastic comprising a polymer P selected from the group consisting of polyalkyl methacrylate, polycycloalkyl methacrylate, polycycloalkyl acrylate and polyalkyl acrylate or at least one copolymer CP produced of at least one monomers M, particularly two monomers M, particularly selected from the group consisting of an alkyl methacrylate, an alkyl acrylate, a cycloalkyl methacrylate and a cycloalkyl acrylate, wherein the cycloalkyl methacrylate and the cycloalkyl acrylate are unsubstituted or substituted with at least
  • the polymer P of the soft polymer A and/or the polymer P of the hard polymer B is selected from the group consisting of poly-Ci- -alkyl methacrylate, poly-Ci-10- alkyl acrylate, poly-Cs-is-cycloalkyl methacrylate und poly-Cs-is-cycloalkyl acrylate.
  • the polymer P of the soft polymer A polyethyl methacrylate (PEMA) and/or a polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA).
  • PEMA polyethyl methacrylate
  • PEMA-PMMA polyethyl methacrylate-polymethyl methacrylate copolymer
  • the polymer P of the hard polymer B is polymethyl methacrylate (PMMA) and/or a polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA).
  • the copolymer CP is derived from monomers M selected from the group consisting of methyl methacrylate, ethyl methacrylate, ethyl acrylate, ethoxyethyl acrylate, tetrahydrofurfuryl methacrylate, tetrahydrofurfuryl acrylate, isobornyl acrylate, isobornyl methacrylate, Ethylene dimethacrylate and ethoxyethyl methacrylate, particularly from the group consisting of 2-ethoxymethacrylate, 2-ethoxy acrylate, tetrahydrofurfuryl acrylate and tetrahydrofurfuryl methacrylate.
  • the polymer P of the soft polymer A polyethyl methacrylate (PEMA) and/or a polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA) and the copolymer CP is derived from monomers M selected from the group consisting of methyl methacrylate, ethyl methacrylate, ethyl acrylate, ethoxyethyl acrylate, tetrahydrofurfuryl methacrylate, tetrahydrofurfuryl acrylate, isobornyl acrylate, isobornyl methacrylate and ethoxyethyl methacrylate, particularly from the group consisting of 2-ethoxymethacrylate, 2- ethoxy acrylate, tetrahydrofurfuryl acrylate and tetrahydrofurfuryl methacrylate.
  • monomers M selected from the group consisting of methyl methacrylate, ethy
  • the polymer P of the hard polymer B is polymethyl methacrylate (PMMA) and/or a polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA) and the copolymer CP is derived from monomers M selected from the group consisting of methyl methacrylate, ethyl methacrylate, ethyl acrylate, ethoxyethyl acrylate, tetrahydrofurfuryl methacrylate, tetrahydrofurfuryl acrylate, isobornyl acrylate, isobornyl methacrylate and ethoxyethyl methacrylate, particularly from the group consisting of 2-ethoxymethacrylate, 2- ethoxy acrylate, tetrahydrofurfuryl acrylate and tetrahydrofurfuryl methacrylate.
  • PMMA polymethyl methacrylate
  • PEMA-PMMA polyethyl methacryl
  • the soft polymer A of the flexible phase FP is a polymer, such as Thermeo®, derived from a first component FCA comprising a polyethyl methacrylate polymer (PEMA) or a polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA), and a second component SCB comprises at least one alkyl acrylate and/or one alkyl methacrylate monomer in which the polyethyl methacrylate polymer (PEMA) or the polyethyl methacrylate- polymethyl methacrylate copolymer (PEMA-PMMA) of component FCA is at least partially soluble, wherein the alkyl acrylate and/or alkyl methacrylate monomer of component SCB is at least one monomer of the group methyl methacrylate, ethyl methacrylate, ethyl acrylate, ethoxyethyl acrylate, tetrahydro
  • the mass ratio of components FCA and SCB is 0.5 - 2.
  • the hard polymer B of the stiff phase SP is a polymer, derived from a first component FCA comprising a polymethyl methacrylate (PMMA) or polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA), and a second component SCB comprises at least one alkyl acrylate and/or one alkyl methacrylate monomer, in which the polyethyl methacrylate polymer (PMMA) or the polyethyl methacrylate-polymethyl methacrylate copolymer (PEMA-PMMA) of component FCA is at least partially soluble, wherein the alkyl acrylate and/or alkyl methacrylate monomer of component SCB is at least one monomer of the group methyl methacrylate, ethyl methacrylate, Ethylene dimethacrylate, tetraethylene glycol dimethacrylate, ethyl acrylate, ethoxyethyl
  • the soft polymer A comprises as a polymer P at least 10 % polyethyl methacryate (PEMA), particularly 20 % polyethyl methacrylate (PEMA), more particularly the soft component A comprises at least 30 % polyethyl methacrylate (PEMA), wherein the soft component A may further comprise polymethyl methacrylate (PMMA).
  • PEMA polyethyl methacryate
  • PEMA polyethyl methacrylate
  • PMMA polymethyl methacrylate
  • the hard component B comprises at least 60 % polymethyl methacrylate (PMMA), particularly the hard component B comprises at least 80 % polymethyl methacrylate (PMMA).
  • the hard component B may further comprise polyethyl methacrylate (PEMA).
  • the flexible phase FP and/or stiff phase SP further comprises an initiator, a plasticiser and an activator.
  • the milling blank comprises layers which generate a hardness gradient in Z-direction through the flexible phase FP and the stiff phase SP.
  • the milling blank comprises a hardness gradient in Z-direction through the flexible phase FP and the stiff phase SP.
  • the Shore hardness of the flexible phase FP is between 20 Shore A and 45 Shore D at body temperature. In other embodiments, the Shore hardness of the flexible phase FP is between 20 Shore A and 40 Shore D at body temperature. In other embodiments, the Shore hardness of the flexible phase FP is between 20 Shore A and 35 Shore D at body temperature. In other embodiments, the Shore hardness of the flexible phase FP is between 20 Shore A and 30 Shore D at body temperature. In other embodiments, the Shore hardness of the flexible phase FP is between 20 Shore A and 25 Shore D at body temperature.
  • the Shore hardness of the stiff phase SP is at least 60 Shore D at body temperature, particularly wherein the Shore hardness of the stiff phase SP is 60 to 95 Shore D, more particularly the Shore hardness of the stiff phase SP is 60 to 90 Shore D. In certain embodiments, the Shore hardness of the stiff phase SP is between 60 to 85 Shore D at body temperature. In further embodiments, the Shore hardness of the stiff phase SP is between 60 to 80 Shore D at body temperature.
  • the hardness gradient between the softest point of the flexible phase FP and the stiffest point of the stiff phase SP is at least 15 Shore D.
  • the flexible phase FP and the stiff phase SP are directly connected to each other, particularly polymerised together, more particularly polymerised through pressure and heat. In further embodiments, the flexible phase FP and the stiff phase SP are directly connected to each other, particularly polymerised together, more particularly polymerised through pressure and heat in an alternating fashion.
  • the flexible phase FP and the stiff phase SP form an equal wave like structure or a planar structure. In certain embodiments, the flexible phase FP is planar and the stiff phase SP forms a wave like structure.
  • the flexible phase FP and the stiff phase SP form an equal wave like structure .
  • each of the two phases of flexible phase FP and stiff phase SP can be arranged such that a desired milling blank can be generated.
  • the stiff phase SP spans the entire base of the milling blank, wherein the flexible phase FP is arranged such on top of the stiff phase SP that it only covers those parts necessary for generating a milling blank. This can for example be advantageous in order to save material and subsequently reduce waste.
  • Fig. 1 a flexible phase A and a stiff phase B (striped) of a milling blank with flat interface in view from the side,
  • Fig. 2 cut-view through a 2-component milling blank with a milled dental splint with a flexible phase A and a stiff phase B (striped),
  • Fig. 3 structured part (flexible phase A) of a 2-component round milling blank
  • Fig. 4 2-component milling blank consisting of a flexible phase A and stiff phase B
  • Fig. 5 sectional view of a structured 2-component milling blank
  • Fig. 6 cross-sectional view through a structured 2-component round plate.
  • FCA and SCB are used for generating the flexible phase, wherein exemplary compositions of which are shown in the table below.
  • a milling blank with a diameter of 98 mm and a thickness of 18 mm is obtained.
  • Test specimens with dimensions 5x5x80 mm are then generated from this milling blank using a milling machine (Otofab 1 , pro3dure). Alternatively, the production of medical molded parts takes place on the basis of 3-dimensional data.
  • the test specimens are then tempered at 23 °C and 37 °C for 24 h and then bent through 90° in the center. The relaxation of the angle is subsequently recorded time-dependently at the two above-mentioned temperatures in order to document the temperature-dependent memory effect. It is shown that the formulation according to the invention comprises a temperaturedependent memory effect by means of which molded bodies, which are deformed at room temperature, almost return to their original shape due to body heat.
  • FCA and SCB are used for generating the stiff phase, wherein exemplary compositions of which are shown in below.
  • Methacrylic acid methyl ester up to 90
  • Di(meth)acrylate e.g. tetraethylene glycol up to 10 dimethacrylate
  • Crosslinker > 3 functional acrylate and or up to 10 methacrylate groups
  • Both Phases are polymerized to each other under the action of pressure and heat to create a direct chemical bonding of the two materials.

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  • Health & Medical Sciences (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Public Health (AREA)
  • Chemical & Material Sciences (AREA)
  • Veterinary Medicine (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Epidemiology (AREA)
  • Dentistry (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Organic Chemistry (AREA)
  • Medicinal Chemistry (AREA)
  • Polymers & Plastics (AREA)
  • Plastic & Reconstructive Surgery (AREA)
  • Materials For Medical Uses (AREA)

Abstract

La présente invention concerne une ébauche de fraisage pour générer une attelle, comprenant au moins deux phases, en particulier une phase flexible FP et une phase rigide SP, caractérisée en ce que la phase rigide SP a une dureté Shore plus élevée à la température corporelle que la phase flexible FP à la température corporelle, à savoir au moins 15 Shore D plus élevée.
PCT/EP2024/056705 2023-03-13 2024-03-13 Ébauche de fraisage à composants multiples Pending WO2024189100A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP23161631.9 2023-03-13
EP23161631 2023-03-13

Publications (1)

Publication Number Publication Date
WO2024189100A1 true WO2024189100A1 (fr) 2024-09-19

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ID=85640834

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2024/056705 Pending WO2024189100A1 (fr) 2023-03-13 2024-03-13 Ébauche de fraisage à composants multiples

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WO (1) WO2024189100A1 (fr)

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20180055611A1 (en) * 2016-07-05 2018-03-01 Dentsply Sirona Inc. Multiple layered denture block and/or disk
US20200308332A1 (en) * 2014-10-14 2020-10-01 Pro3dure Medical GmbH Milling blank for the production of medical-technical molded parts
US20210128283A1 (en) * 2017-08-16 2021-05-06 Gc Corporation Denture block

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20200308332A1 (en) * 2014-10-14 2020-10-01 Pro3dure Medical GmbH Milling blank for the production of medical-technical molded parts
US20180055611A1 (en) * 2016-07-05 2018-03-01 Dentsply Sirona Inc. Multiple layered denture block and/or disk
US20210128283A1 (en) * 2017-08-16 2021-05-06 Gc Corporation Denture block

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