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Material, Dental Impression

Dental impression materials are substances used to create a negative mold of the teeth and surrounding structures.
These materials, often made of silicones, alginates, or polyvinyl siloxanes, capture the precise details of the oral cavity for the fabrication of dental prosthetics, such as crowns, bridges, and dentures.
The selection and use of the appropriate impression material is crucial for ensuring the accuracy and fit of the final dental restorations.
Researchers continuin to optimize impression protocols to enhance reproducibilty and accuracy, leveraing AI-driven comparisons to identify the best materials and techniques.

Most cited protocols related to «Material, Dental Impression»

1
Temporal Bone Preparation for Cochlear Implant Studies
Temporal bone preparation and experimental procedures were similar to methods described previously by our laboratory (29 (link)–31 (link)), as well as other authors (23 (link)), modified accommodate for the preparation and experimental time required for using whole head specimens. Preparation and experimentation were typically completed on separate days, thus in order to minimize degradation to the tissue, the following schedule was followed for hemi-cephalic/whole head specimens. First, specimens were thawed and temporal bones were prepared in one or both ears and refrozen within approximately 12 or 24 hours. Second, specimens were rethawed; one ear was tested within approximately 12 hours in hemicephalic, and both ears were tested during the course of two consecutive days (~48 h) in whole heads. The total duration that each specimen was left at room temperature was < ~24 hours for hemi-cephalic, and < 72 hours in whole head specimens.
Temporal bones were prepared using the following procedure: specimens were thawed in warm water, and the external ear canal and tympanic membrane were inspected for damage. A canal-wall-up mastoidectomy and extended facial recess approach was performed to visualize the incus, stapes, and round window (30 (link)). The cochlear promontory near the oval and round windows was thinned with a small diamond burr in preparation for pressure sensor insertion into the scala vestibuli (SV) and scala tympani (ST).
Cochleostomies into the ST and SV were created under a droplet of water using a fine pick. Pressure sensors (FOP-M260-ENCAP, FISO Inc., Quebec, QC, Canada), were inserted into the SV and ST using rigidly mounted micromanipulators (David Kopf Instruments, Trujunga, CA). Pressure sensor diameter is approximately 310 μm (comprised of a 260 μm glass tube covered in polyimide tubing with ~25 μm wall thickness), and are inserted into the cochleostomy until the sensor tip is just within the bony wall of the cochlea (~100 μm). Cochleostomies were made as small as possible, such that the pressure probes fit snuggly within, but inserted completely into the opening. Pressure sensor sensitivity is rated at ± 1 psi (6895 Pa). The signal is initially processed by a signal conditioner (Veloce 50; FISO Inc., Quebec, QC, Canada), which specifies the precision and resolution of at 0.3% and 0.1% of full scale, or ~20.7 Pa and 6.9 Pa respectively. Sensors were sealed within the cochleostomies with alginate dental impression material (Jeltrate; Dentsply International Inc., York, PA). Location of the cochlostomies with respect to the basilar membrane were verified visually after each experiment by removing the bone between the two cochleostomies.
Out-of-plane velocity of VStap was measured with a single-axis LDV (OFV-534 & OFV-5000; Polytec Inc., Irvine, CA) mounted to a dissecting microscope (Carl Zeiss AG, Oberkochen, Germany). Microscopic retro-reflective glass beads (Polytec Inc., Irvine, CA) were placed on the neck and posterior crus of the stapes to ensure a strong LDV signal since the stapes footplate was typically obscured by the presence of the stapes tendon. In all LDV measurements, the position of the laser was held as constant as possible between experimental conditions (32 (link),33 (link)).
CI electrodes used in these experiments were: Nucleus Hybrid L24 (HL24; Cochlear Ltd, Sydney, Australia), Nucleus CI422 Slim Straight inserted at 20 and 25 mm (SS20 & SS25; Cochlear Ltd, Sydney, Australia), Nucleus CI24RE Contour Advance (NCA; Cochlear Ltd, Sydney, Australia), HiFocus Mid-Scala (MS; Advanced Bionics AG, Stäfa, Switzerland), and HiFocus 1j (1J; Advanced Bionics AG, Stäfa, Switzerland). Electrode dimensions are provided in Table 1. Electrodes were inserted sequentially, under water, into the ST via a RW approach. Electrodes were typically inserted in order of smallest to largest (i.e. the order listed above) in an attempt to minimize the effects of damage caused by insertion on subsequent recordings. Potential effects of insertion order are expected to be minimal, owing to the similarity in responses across conditions (see Results), and the lack of any observable effect in one experiment in which the electrode insertion order was shuffled. The cochleostomy was sealed following each electrode insertion with alginate dental impression material, and excess water was removed via suction from the middle ear cavity.
Greene N.T., Mattingly J.K., Jenkins H.A., Tollin D.J., Easter J.R, & Cass S.P. (2015). Cochlear Implant Electrode Effect on Sound Energy Transfer within the Cochlea during Acoustic Stimulation. Otology & neurotology : official publication of the American Otological Society, American Neurotology Society [and] European Academy of Otology and Neurotology, 36(9), 1554-1561.
Publication 2015
Alginate ARID1A protein, human Basilar Membrane Bones Cell Nucleus Cochlea Dental Caries Dentsply Diamond Ear Epistropheus External Auditory Canals Face Fenestra Cochleae Head Hybrids Hypersensitivity Incus Jeltrate Labyrinths, Bony Leg Mastoidectomy Material, Dental Impression Microscopy Middle Ear Neck Pressure Pulp Canals Scala Tympani Stapes Suction Drainage Temporal Bone Tendons Tissues Tympanic Membrane Vestibuli, Scala
2
Finite Element Analysis of Removable Partial Dentures
Experimental procedures were approved by the West China Hospital of Stomatology, Sichuan University (reference number WCHSIRB-D-2018-105). All methods were performed in accordance with the relevant guidelines and regulations in the informed consent. And the informed consent was gotten to publish identifying information including CBCT and oral master model. A 3-dimensional FEA solid model of lower jaw was constructed using clinical CBCT data and master model scanned data from a 53-year-old Chinese patient with bilateral dissociation deletion of Kennedy Class I. Oral examination showed a severely absorbed mandibular bone with 34–37, 31–43, 46, and 47 teeth missing (FDI standard), and no other abnormality was discovered among the remaining teeth. The modeling steps are shown in Fig. 3.

The flow chart of modeling.

The mandibular bone was scanned with CBCT (3D Accuitomo scanner, Morita, Kyoto, Japan) at a 0.25-mm-slice thickness and 1-mm scan increment in 401 slice images in DICOM format. The images were imported into the Mimics (Mimics 17.0, Materialise NV) to obtain the mandibular bone model and the remaining teeth models. The output data were then imported to Geomagic Studio (Geomagic Studio12.0, Geomagic Co, USA) for surface reconstruction. The remaining teeth models A (RTMA) and mandibular bone model A (MBMA) were obtained for further use.
The mandibular impression was made by using alginate impression materials, and the master model was made with plaster. The features of oral mucosa were obtained by scanning the master model with a desk scanner (3shape D2000, Denmark), and the obtained data were imported to Geomagic Studio for surface reconstruction. Digitalized master model (DMM) was obtained for further use.
RTMA, MBMA and DMM were aligned in Geomagic Studio by matching three matching points on the remaining teeth surfaces of RTMA and DMM. Boolean operation was first used to remove the exposed part of bone of MBMA to obtain the final mandibular bone model (FMBM). Boolean operation was then used to remove the remaining crowns on the DMM by subtracting it with RTMA, and the final mucosal model (FMM) was obtained. The mucosa thickness was defined with the vertical distance between the mandibular bone surface and the mucosal surface. The 3D oral model obtained with this technique can provide a more accurate geometrical morphology and thickness of mucosa, which is crucial for RPD simulation. The PDL was simulated by adding a 0.2 mm thick shell to the interface area between bone and tooth models, and then the volume shell is subtracted from the bone in order to define the PDL volume as previous studies proposed41 (link),42 (link). Following the design specifications for RPDs, 4 kinds of RPDs were designed by an experienced prosthodontist as well as technician together by using 3shape Dental System software (Dental system 2017, Denmark). Figure 4 demonstrated the 4 different designs of frameworks, and the designs are as follows:

4 Different designs of frameworks.

Framework A: an RPT (Rest-Plate-T bar) clasp set in the canine of left mandibular region; an RPI (Rest-Plate-I bar) clasp set in the second premolar of right mandibular region.
Framework B: an RPT (Rest-Plate-T bar) clasp set in the canine of left mandibular region; an arrow clasp between the premolars of the right mandibular region.
Framework C: an RPT (Rest-Plate-T bar) clasp set in the canine of left mandibular region; an RPL (Rest-Plate-L bar) clasp set in the first premolar of right mandibular region; a back-action clasp in the second premolar of right mandibular region.
Framework D: an Aker clasp in the canine of left mandibular region; a combined clasp between the premolars of right mandibular region.
The FMBM, FMM, RTMA and all the frameworks, denture bases and denture teeth models were then processed by Abaqus/CAE (2016, SIMULIA Co, USA) to convert into a three-dimensional FEA solid model (Fig. 5). The ten-node tetrahedral elements were selected for the models. A convergence study was carried out to determine the optimal size of elements. In Fig. 6, the influence of the size of elements on the maximum Von-Mises stress and maximum displacement of the model is presented. It shown that the stress and displacement were converged as the element size smaller than 0.2 mm. As a result, the size of elements can be located as 0.2 mm.

Final components of the model.

Convergence study: Influence of the size of elements on maximum Von-Mises stress and maximum displacement of finite element model.

All materials except the PDL were assumed to be linearly elastic, homogenous and isotropic to simplify the calculations. Table 1 showed the elastic modulus and the Poisson ratio for each material43 (link)–45 . As for the PDL, the nonlinear hyper-elastic model was used based on the double linear stress-strain curve of Vollmer’s28 research: when the dependent variable of PDL ɛ < 7.5%, E1 = 0.05 MPa; and when ɛ > 7.5%, E2 = 0.22 MPa. Also, there are several studies used nonlinear parameters with mucosa, previous studies showed that with RPD scenario, the simulation results with linear mucosa parameter were highly correspondence with in vitro test results with sensors46 (link), indicating linear parameter of mucosa is acceptable under normal occlusal force with RPD scenario. There are also several studies used the same method to investigate the stress and displacement of mucosa with RPD, which can simplify calculation process as well as obtain accurate results20 (link),47 (link),48 (link).

Material properties of finite element models.

MaterialElastic Modulus (MPa)Poisson Ratio
Mucosa3.450.45
Denture Base2,2000.31
Cancellous Bone1,3700.30
Cortical Bone13,7000.30
PDLNon-linear (see below)0.45
Tooth Dentin18,6000.30
Denture Tooth1,9600.30
Co-Cr Alloy235,0000.33
Titanium Alloy11 * 1040.35
PEEK4,1000.4
The tooth was simplified as a uniform dentine material without concerning about the difference between the dentine and the enamel, as the mechanical property of these two materials are proved to be similar in the previous study49 (link). The PDLs and teeth roots, the denture teeth and denture base were considered as position constraints. The interfaces between the clasps and the remaining teeth were modeled as frictional contacts with appropriate friction coefficients (μ = 0.1), and the friction coefficients between the denture base and mucosa was assumed as μ = 0.0143 (link),44 .
To simulate an occlusal force, a vertical load of 120 N was applied to the occlusal surface of both the artificial first molar39 (link). Although different masticatory activities (e.g. grinding) with various loading patterns may affect the optimization outcome, but the effects of other masticatory activities are less significant compared to the direct biting force because of the magnitudes50 (link). The following were investigated: the von Mises stress values of the PDLs, mucosa, frameworks, and the displacement of frameworks. Data were exported to SPSS 19.0 (IBM, Chicago, USA) for statistical analysis. One-way ANOVA and the Student-Newman-Keuls q test was used to determine differences among different framework materials and different framework design schemes. For all comparisons, statistical significance was declared if p < 0.05.
Chen X., Mao B., Zhu Z., Yu J., Lu Y., Zhang Q., Yue L, & Yu H. (2019). A three-dimensional finite element analysis of mechanical function for 4 removable partial denture designs with 3 framework materials: CoCr, Ti-6Al-4V alloy and PEEK. Scientific Reports, 9, 13975.
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Publication 2019
Alginate Bicuspid Bones Canis familiaris Chinese Crowns Deletion Mutation Dental Enamel Dental Health Services Dental Materials Dentin Denture Bases Dentures Friction Homozygote In Vitro Testing Mandible Material, Dental Impression MM-401 Models, Dental Mucosa, Mouth Mucous Membrane neuro-oncological ventral antigen 2, human Oral Examination Patients Prosthodontists Reconstructive Surgical Procedures Strains Student Tooth Tooth Root
3
Temporal Bone Preparation and Measurement
Temporal bone preparation was similar to methods described previously by our laboratory [13 (link),14 (link)], as well as other authors [10 (link)]. The specimens were thawed in warm water, and inspected for any damage. A canal-wall-up mastoidectomy and extended facial recess approach was performed to visualize the incus, stapes, and RW [10 (link)]. The cochlear promontory near the oval and round windows was thinned with a small diamond burr in preparation of pressure sensor insertion into the scala vestibuli (SV) and scala tympani (ST). A BI300 4 mm titanium implant fixture (Cochlear Americas, Centennial, CO) was placed on temporal line approximately 55 mm from the external auditory canal (EAC).
The full cephalic specimens were fastened to a Mayfield Clamp (Integra Lifesciences Corp., Plainsboro, NJ) attached to a stainless steel baseplate. Cochleostomies into the ST and SV were created under a droplet of water using a fine pick. Pressure sensors (FOP-M260-ENCAP, FISO Inc., Quebec, QC, Canada), were inserted into the SV and ST using micromanipulators (David Kopf Instruments, Trujunga, CA) mounted on the Mayfield Clamp, and sealed to the cochlea with alginate dental impression material (Jeltrate; Dentsply International Inc., York, PA).
Out-of-plane velocity of the middle ear structures was measured with a single-axis LDV (OFV-534 & OFV-5000; Polytec Inc., Irvine, CA) mounted to a dissecting microscope (Carl Zeiss AG, Oberkochen, Germany). Microscopic retro-reflective glass beads (Polytec Inc., Irvine, CA) were placed on the stapes, RW, and cochlear promontory to ensure a strong LDV signal. In all LDV measurements, the position of the laser was held as constant as possible between experimental conditions, though slight shifts were unavoidable when swapping implants [15 –16 (link)].
Mattingly J.K., Greene N.T., Jenkins H.A., Tollin D.J., Easter J.R, & Cass S.P. (2015). Effects of Skin Thickness on Cochlear Input Signal using Transcutaneous Bone Conduction Implants. Otology & neurotology : official publication of the American Otological Society, American Neurotology Society [and] European Academy of Otology and Neurotology, 36(8), 1403-1411.
Publication 2015
Alginate ARID1A protein, human Cochlea Dentsply Diamond Epistropheus External Auditory Canals Face Fenestra Cochleae Incus Jeltrate Mastoidectomy Material, Dental Impression Microscopy Middle Ear Pressure Pulp Canals Scala Tympani Stainless Steel Stapes Temporal Bone Titanium Vestibuli, Scala
4
Fracture Toughness of Denture Reline Resins
One denture base acrylic resin (Lucitone 550) and four autopolymerizing reline resins (Ufi
Gel Hard, Tokuyama Rebase II, New Truliner and Kooliner) were evaluated in this study. The
product codes, batch numbers, manufacturers, compositions, powder/liquid proportions and
polymerization cycles of the materials evaluated are listed in Figure 1.
Specimens from each material were produced using a stainless steel mold with a cavity (40
mm×8 mm×4 mm)28 (link). To fabricate the Lucitone
550 specimens, initially, the silicone impression material was adapted inside the stainless
steel mold. The silicone patterns were then removed from the mold, placed between two glass
slides and invested in Type IV stone using a conventional dentureprocessing flask. After the
stone had set, the flask was opened and the silicone patterns were removed to create the
stone molds. The Lucitone 550 heatpolymerized resin was then manipulated, packed into the
stone mold, and polymerized in a water bath following the manufacturer's instructions (Figure 1). Then the flasks were removed from the water
bath and bench cooled to room temperature before the specimens were removed. After
polymerization, the specimens were finished with 320-grit silicon carbide paper to remove
irregularities; then the accuracy of the dimensions was verified with a caliper. The
specimens were then stored in water at 37ºC for 48±2 hours19 .
To prepare the specimens of the autopolymerizing reline resins (UH, TR, NT and K), the
stainless steel mold was placed on the center of a glass plate covered with an acetate
sheet. The autopolymerizing reline resins were mixed according to the manufacturer's
instructions, and placed into the mold spaces (40 mm×8 mm×4 mm). A second acetate sheet was
placed on top of the resin and another glass plate was placed on top of the acetate sheet.
Light pressure was applied to expel excess material from the mold, and the materials were
polymerized according to the manufacturers' instructions (Figure 1). After polymerization, any excess material was removed using silicon
carbide paper (320-grit), and the dimensions were verified with a caliper.
For the fracture toughness measurements, the method used by Zappini, Kammann and
Watcher28 (link) (2003) and Puri, et
al.26 (link) (2008) was followed. The test
requires a sharp-notched specimen loaded in a three-point bending configuration which is
also known as the single edge-notched bend (SENB) method28 (link). Thus, a 0.5-mm-wide notch, 3.0 mm in length, was machined in the
center of each specimen and then sharpened using a razor blade to extend the notch another
0.1 to 0.2 mm26 (link). The specimens of each
material (n=20) were then divided into two groups: one control (CG) and one experimental
(TG). For the UH, TR, NT and K autopolymerizing reline resins, the specimens were subjected
to fracture toughness tests (GC group), or to the thermal cycling prior to the fracture
toughness tests (TG group), within 30 min after polymerization. This time period was used
since the patients will be wearing the relined denture bases soon after polymerization. For
the L denture base material, the specimens were subjected to fracture toughness tests (GC
group), or to the thermal cycling prior to the fracture toughness tests (TG group), after
storage in distilled water at 37±1ºC for 48±2 h19 . Thermal cycles were performed in a thermocycling machine (model
MSCT-3, Marcelo Nucci - Me, São Carlos, SP, Brazil) and consisted of 5000 cycles at 5ºC and
55ºC with a 30-second dwell time14 (link).
Fracture toughness measurements were carried out in a universal testing machine (MTS 810,
MTS Systems Corporation, eden Prairie, MN, USA) in a three-point bending configuration at a
cross-head speed of 1 mm/min and a 32-mm specimen test span26 (link),28 (link). The toughness test
was carried out in a water bath at 37±1ºC.
The maximum stress intensity factor (KI,max) was calculated using the following
formula28 (link): KI,max
=f Pmax/(B W1/2),
where Pmax is the maximum load, B is the specimen thickness, Wis the specimen width, and f is a geometrical factor depending on the ratio
(a/W. KI,max was expressed in MPa.m1/2.
Data were analyzed using the two-way ANOVA and Tukey's tests (p=0.05). The
software package used for statistical analysis was the SPSS version 16.0 for Windows
(Chicago, IL, USA).
SILVA C.D., MACHADO A.L., CHAVES C.D., PAVARINA A.C, & VERGANI C.E. (2013). Effect of thermal cycling on denture base and autopolymerizing reline resins. Journal of Applied Oral Science, 21(3), 219-224.
Publication 2013
Acetate Acrylic Resins Bath Calculi Dental Caries Denture Bases Fracture, Bone Fungus, Filamentous Head kooliner Light Lucitone Material, Dental Impression neuro-oncological ventral antigen 2, human NOTCH2 protein, human Patients Polymerization Powder Pressure Resins, Plant Silicones Stainless Steel Steel truliner
5
Temporal Bone Preparation and Pressure Measurement
A detailed description of the temporal bone preparation has appeared previously (16 (link),20 (link)), and were similar to methods described previously by our laboratory (21 (link)–23 (link)), as well as other authors (24 (link)). Briefly, specimens were thawed in warm water, a canal-wall-up mastoidectomy and extended facial recess approach was performed, and the cochlear promontory was thinned near the oval and round windows. Figure 1 shows the facial recess exposure from one specimen (427L). Cochleostomies into the scala tympani (ST) and scala vestibuli (SV) were created, after blue-lining the cochlear promontory (Figure 1A), using a fine pick under a droplet of water (Fig. 1B). Commercially available, off-the-shelf fiber-optic pressure sensors (FOP-M260-ENCAP, FISO Inc., Quebec, QC, Canada), similar to those used in several recent studies in our lab and elsewhere (16 (link), 20 (link), 25 ), were inserted (Fig. 1C), and sealed with alginate dental impression material (Jeltrate; Dentsply International Inc., York, PA). Pressure probe placements and approximate location of the basilar membrane were verified after each experiment by dissecting out the cochlear promontory bone between the two cochleostomy sites (Fig. 1D). Note: it was not always possible to differentiate individual components of the cochlear partition, such as the basilar membrane or the spiral lamina; however, manipulation with a pick verified that it was soft tissue and not bony - hereafter we refer to this partition simply as the basilar membrane. Out-of-plane velocity of the stapes (VStap) was measured with a single-axis LDV (OFV-534 & OFV-5000; Polytec Inc., Irvine, CA) mounted to a dissecting microscope (Carl Zeiss AG, Oberkochen, Germany). Microscopic retro-reflective glass beads (P-RETRO 45–63 μm dia., Polytec Inc., Irvine, CA) were placed on the neck and posterior crus of the stapes to ensure a strong LDV signal since the stapes footplate was typically obscured by the presence of the stapes tendon. Velocity measurements are not presented in this report.
Greene N.T., Mattingly J.K., Banakis Hartl R.M., Tollin D.J, & Cass S.P. (2016). Intracochlear pressure transients during cochlear implant electrode insertion. Otology & neurotology : official publication of the American Otological Society, American Neurotology Society [and] European Academy of Otology and Neurotology, 37(10), 1541-1548.
Publication 2016
Alginate Basilar Membrane Bones Cochlea Dentsply Epistropheus Face Fenestra Cochleae Jeltrate Labyrinths, Bony Leg Mastoidectomy Material, Dental Impression Microscopy Neck Pressure Pulp Canals Scala Tympani Spiral Lamina Stapes Temporal Bone Tendons Tissues Vestibuli, Scala

Most recents protocols related to «Material, Dental Impression»

1
Microscopy Techniques for Cladode Analysis
Samples for light and transmission electron microscopy were prepared according to Kondo et al. (1998 (link)). Small segments of cladode chlorenchyma were fixed immediately in 3% (v/v) glutaraldehyde in 50 mM sodium phosphate (pH 6.8) for 1.5 h, washed in phosphate buffer, post-fixed in 2% OsO4 in buffer, dehydrated through an acetone series, and embedded in Spurr’s resin. Ultrathin sections were stained with uranyl acetate and lead citrate, and analyzed at 80 kV acceleration voltage under a transmission electron microscope (TEM, model JEM-1011, JEOL Ltd., Tokyo, Japan). Semithin sections were stained with 1% toluidine blue O.
The thicknesses of the cell wall and cuticle (the cutin and wax layers) were measured using ImageJ software (National Institutes of Health, Bethesda, MD, USA) at 18 points (3 points × 2 sections × 3 plants per treatment) at × 50,000 magnification.
For scanning electron microscopy, epoxy replicas of epidermal cells were prepared according to Green and Linstead (1990 (link)). Dental impression material (Extrude Wash, Kerr Corp., Orange, CA, USA) was applied to the cladode surfaces, incubated for 5 min, and peeled off. The negative molds were filled with epoxy resin (2-Ton Epoxy S-31; Devcon Corp., MA, USA), polymerized for 24 h at room temperature, coated with gold and palladium at 10–15 nm thickness, and analyzed at 10–20 kV acceleration voltage under a scanning electron microscope (SEM, model JSM-IT100, JEOL Ltd.).
Cuticular wax coverage (% of cuticular wax per 1.2 mm2 surface area of the cladode) was measured using ImageJ software. The procedure included the following steps: (i) cuticular wax was segmented by [Threshold] on the sample image; if segmentation was difficult, a region of cuticle wax was selected with [Polygon selections] and [Cut] to crop it out, leaving a black area; (ii) [Threshold] was adjusted to obtain a black-and-white binarized image; (iii) the area of segmented cuticular wax was analyzed by [Analyze Particles], and cuticular wax coverage was determined as a percentage of the total image area. The coverage was calculated as the mean of 6 measurements (2 sections × 3 plants per treatment) at × 100 magnification.
Kondo A., Ito M., Takeda Y., Kurahashi Y., Toh S, & Funaguma T. (2023). Morphological and antioxidant responses of Nopalea cochenillifera cv. Maya (edible Opuntia sp. “Kasugai Saboten”) to chilling acclimatization. Journal of Plant Research, 136(2), 211-225.
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Publication 2023
Acceleration Acetone Buffers Cell Wall Citrates Crop, Avian cutin Epidermal Cells Epoxy Resins Extrude Fungus, Filamentous Glutaral Gold Light Material, Dental Impression Palladium PER1 protein, human Phosphates Plants Scanning Electron Microscopy sodium phosphate spurr resin Tolonium Chloride Transmission Electron Microscopy uranyl acetate
2
Evaluating 3D Printing Accuracy for Dental Models
An arch-shaped master model measuring 14 mm in height and 16 mm in width was designed using CAD software (RapidForm XOR2; 3D Systems). Six abutments representing prepared teeth (right and left mandibular second molar, right and left mandibular second premolar, right and left mandibular canine) with a height of 10.15 mm and 6° total angle of convergence with 1mm shoulder finish line were placed on the arch. The abutments were designed according to ANSI /ADA specifications, which are also similar to abutments on the test model used in ISO 12836:2015 specification (Digitizing devices for CAD/CAM systems for indirect dental restorations-Test methods for assessing accuracy) [16 (link)].
The digital master model was then saved in Standard Tessellation Language (.stl) format and printed using a Polyjet 3D printer (Objet30 Prime, Stratasys Ltd.). The Polyjet 3D printers utilize materials that are extruded from nozzles or a photopolymer that is jetted over the workspace. Then the object is solidified through polymerization with the use of a UV light source [17 (link)]. The Objet30 Prime printer uses the intuitive “Objet Studio” 3D printing software. A rigid and transparent photopolymer material named VeroClear was used to print the master model, while the SUP705 material was used for support structures. The SUP705 material is removable with a waterjet, so no post-curing process was necessary. The production time of the master model took 4 hours and 10 minutes.
An industrial structured blue LED light 3D scanner (ATOS Core 200 5M, GOM GmbH, Braunschweig, Germany) was selected for use. The scanner was calibrated and tested according to VDI/VDIE 2634 (VDI e.V.; Düsseldorf, Germany), displaying maximum deviations: 2 μm probing error form (sigma), 4 μm probing error (size), 7 μm sphere spacing error and 8 μm length measurement error. The printed master model was then scanned ten times with the ATOS scanner and the scan data was merged into a single file using computer software. The data was then exported in STL format.
Polyvinyl siloxane (PVS) impression material and a one-step impression technique were used for the impression procedure. The impression materials were mixed according to the manufacturer’s instructions. The PVS putty impression material (Vinlybest; BMS DENTAL, Capannoli, Italy) was hand-mixed until a homogeneous mixture was obtained within 30 seconds, and it was then inserted into the customized tray. The light-body material (Vinlylight; BMS DENTAL, Capannoli, Italy) was simultaneously spread on the master model. The impressions were allowed to polymerize, and the trays were removed after the materials had set. A total of 30 impressions were made under the same room conditions and stored at room temperature (22° C) for 2 hours before the pouring procedure. All impressions were examined visually, and impressions with voids were excluded from the study.
The dental gypsum products used in this study included two CAD/CAM optimized stones (CEREC Stone BC, Sirona Dental Systems GmbH Bensheim, Germany) (BC) and (Elite Master, Zhermack S.p.A, Italy) (EM) and one conventional type IV stone (Elite Rock Fast, Zhermack S.p.A, Italy) (ERF) (Fig 1). The composition and characteristics of the materials are summarized in Table 1. All dental stones were mixed according to the respective manufacturer’s recommendations. Deionized water was used. Each stone cast was poured under vibration (Degussa Vibrator R2; Degussa AG, Germany) and allowed to set for 2 hours at room temperature. A total of 30 stone casts were made (n = 10). Then, all stone models were scanned with the Activity 885 blue light scanner (Smart Optics; Bauman Sensortechnik GmbH, Germany, the accuracy of 6 μm according to DIN ISO 12836) [18 (link)], and digital models were obtained.
In the 3D analysis (Geomagic Control, 3D Systems) procedure, a sample size of 15,000 points with a tolerance of 0.001 mm and the best-fit alignment method was used. The 3D analysis software gave the root mean square (RMS) and average maximum and minimum values. Trueness was determined by superimposing the digital master model data on the digital models. Precision was assessed for each digital model by overlaying combinations of the 10 datasets in each group.
The color-coded maps of deviations were created using scans of the stone models. The maps were presented using 3D analysis software. Yellow to red fields represent enlargements, while turquoise to dark blue fields represent contractions on the digital models (Fig 2). The point cloud density of each model was calculated using MeshLab software (ISTI—CNR, Pisa, Italy) (Fig 3). The number of all points that construct the complete digital model was divided by the model’s surface area in mm2.
Statistical analysis was performed with a significance level of 95% and %99 using software NCSS (Number Cruncher Statistical System) 2007 (Kaysville, Utah, USA). The distribution of study data was evaluated with the Shapiro-Wilk Test. Since the assumption of normality was not met, Kruskal Wallis and Mann-Whitney non-parametric tests were used to compare the different dental stones and the statistical analysis of the measurements.
Ceylan G, & Emir F. (2023). Evaluating the accuracy of CAD/CAM optimized stones compared to conventional type IV stones. PLOS ONE, 18(3), e0282509.
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Publication 2023
Bicuspid Calculi Canis familiaris CD3EAP protein, human Cerec Dental Care Dental Gypsum Dental Health Services Eye Human Body Hypertrophy Immune Tolerance Light Mandible Material, Dental Impression Medical Devices Microtubule-Associated Proteins Molar Muscle Rigidity Neoplasm Metastasis Polymerization Radionuclide Imaging reactive blue 15 Shoulder Tooth Tooth Root Ultraviolet Rays Urination Vibration vinyl polysiloxane Zinostatin
3
Fabricating a Retraction Cord Packing Model
We fabricated a stone model with two to six plastic teeth prepared for full crown restorations, as described in the Retraction Cord Model Fabrication Instructional Guide video (Appendix A). Gingival tissue was simulated using medium body polyvinylsiloxane impression material. To maintain cost-effectiveness, teeth that had previously been prepared by students for full crowns were used to fabricate the models. We tested the models with a focus group of five clinical faculty members to preassess them as a teaching tool and aid in developing a postexercise survey. A printed version of the step-by-step Instructional Guide for Fabricating a Retraction Cord Packing Model (Appendix B) was available as an adjunct to the video.
Mills D.A., Fountain A.C, & Velazquez D. (2023). Cord Placement Model: An Instructional Guide for Preclinical Dental Students to Practice the Skill of Retraction Cord Placement. MedEdPORTAL : the Journal of Teaching and Learning Resources, 19, 11303.
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Publication 2023
Calculi Cone-Rod Dystrophy 2 Crowns Gingiva Human Body Material, Dental Impression Student Teaching Tissues Tooth vinyl polysiloxane
4
Fabrication of Dental Stone Model Samples
For the fabrication of study samples, two maxillary jaw teeth set dental stone model was used. The maxillary second molar (Dentona® Esthetic-Base® gold, Dentona AG, Dortmund, Germany) was prepared in the model (the first molar was cut) to receive a circumferential clasp with the desired undercut (Figure 1). The maxillary jaw model was surveyed and an undercut of 0.25 mm on one model and 0.50 mm on the other were created. Occlusal rests (2.5 mm long, 2.5 mm wide, and 2 mm deep) were placed mesially. The prepared molar models were duplicated with silicon impression material (Dublisil, Dreve Den-tamid GmbH, Unna, Germany). The impressions were poured into resin material (RHINO ROOCK, DB Lab Supplies Limited) to fabricate 42 molars models: 21 with a 0.25 mm undercut and 21 with a 0.50 mm undercut [23 (link)].
Vaddamanu S.K., Alhamoudi F.H., Chaturvedi S., Alqahtani N.M., Addas M.K., Alfarsi M.A., Vyas R., Kanji M.A., Zarbah M.A., Alqahtani W.M., Alqahtani S.M., Abdelmonem A.M, & Elmahdi A.E. (2023). Retentive Forces and Deformation of Fitting Surface in RPD Clasp Made of Polyether-Ether-Ketone (PEEK). Polymers, 15(4), 956.
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Publication 2023
Calculi Gold Material, Dental Impression Maxilla Models, Dental Molar Resins, Plant REST protein, human Silicon Tooth
5
Fracture Resistance of Endodontically Treated Premolars
The sample size was calculated in G-power software. Eighty human permanent single-rooted mandibular first and second premolars with fully formed apex extracted for orthodontic purposes were collected from the Department of Oral and Maxillofacial Surgery, after prior ethical approval from the ethical committee (PDCH/19/EC/164). Teeth were examined under a stereomicroscope at a magnification of 45X to check if any crack/craze lines were present, the x-rays were taken to check for calcification, caries, fractured old restoration, resorption defects, and root canal treated teeth, any tooth with these findings was excluded from the study. To ensure homogeneity, teeth with approximately the same weights and same lengths were chosen.
The samples were disinfected by immersing them in 10% formalin solution for seven days and then cleaned using an ultrasonic scalar. Teeth were stored for three months in 0.9% physiologic saline before further use. To prevent the flow of acrylic resin, the roots of each sample were wrapped in a single layer of aluminum foil and then placed vertically in a plastic mold packed up to the level of the cervical margin of the tooth (CEJ) with self-cure acrylic resin. All the specimens were radiographed in mesiodistal and buccolingual directions to ensure vertical positioning in their artificial socket. Just after the polymerization of acrylic resin, the aluminum foil was removed, and roots were coated with light body addition silicone impression material to mimic an artificial periodontal ligament space and placed back into the resin block.
A minimal invasive access cavity was prepared using #4 round bur (Dentsply Maillefer, Switzerland) in such a way that the preparation started usually at the central fissure of the occlusal surface, extended towards pulp with smoothly convergent walls, and canals were located (Figure 1). The patency of the canal was established using a #15 k file (Dentsply Maillefer, Switzerland) followed by working length determination using radiographs. Eighty specimens were distributed randomly and equally divided into four groups (n=20).
Except for the control group, the remaining samples were then instrumented, keeping the apical size of #30 by different taper rotary instruments using the crown-down technique. The groups were as followed, Group 1: samples left uninstrumented, Group 2: instrumented up to 30/.04 taper of K3 rotary file system (Sybron Endo, Orange, CA, USA), Group 3: instrumented up to 30/.06 taper of K3 rotary file system (Sybron Endo, Orange, CA, USA), Group 4: instrumented to 30/.08 taper of K3 rotary file system (Sybron Endo, Orange, CA, USA).
The canals were irrigated with 3% NaOCl and distilled water during instrumentation (Prime dental products, Mumbai, India). Following instrumentation, a final flush of 5 ml 17% EDTA (Pyrax Polymar, India) and 5 ml 2.5% NaOCl was applied for 1 minute, later by a last rinse of 5 ml distilled water for 1 minute using a 27G side-vented needle. The canals were desiccated with paper points and filled three-dimensionally using Fast Pack and Fast-Fill Obturation system (Channgzhou Saifary Medical Technology Co. Ltd., Jiangsu Province, China) and Sealapex sealer (Kerr, Romulus, MI). The gutta-percha was removed from the orifices, cleaned the access with normal saline. The access cavity was etched with 37% phosphoric acid etchant for 30 seconds and thoroughly washed using water spray with a three-way syringe then bonding agent (Coltene-Whaledent, Switzerland), was applied using a micro brush with agitation, and the air was spread slowly onto the bonding agent to get homogenous distribution then cured with LED curing light (SmartLight Pro Dentsply Sirona) for 20 seconds. The access cavity was restored using composite resin in increments according to the manufacturer's instructions (Coltene-Whaledent, Switzerland).
The samples were mounted on a universal testing machine, which used a steel conical tip with a diameter of 0.5mm and a speed of 1.25mm/min, allied with the access cavity's center for each specimen (Figure 2). The load required to cause root fracture was measured in newtons and applied at a crosshead speed until root fracture occurred. For each group, the mean values and standard deviation were calculated. All the data were then statistically evaluated using the One-way Analysis of Variance (ANOVA) test and the Post-hoc Tukey's test. The Statistical Package for the Social Sciences software (SPSS) version 20 was used to analyze the data (SPSS Inc., Armonk, NY). P < 0.05 was chosen as the statistical significance level.
Bapna P., Ali A., Makandar S.D., Nik Abdul Ghani N.R, & Metgud S. (2023). Comparative Evaluation of Fracture Resistance of Endodontically Treated Teeth Instrumented With K3XF Rotary Files Using Different Tapers. Cureus, 15(1), e34247.
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Publication 2023
Acrylic Resins Aluminum Bicuspid Composite Resins Dental Caries Dental Health Services Dental Pulp Dentsply Edetic Acid Endometriosis Flushing Formalin Fracture, Bone Fungus, Filamentous Gomphosis Gutta-Percha Homo sapiens Homozygote Human Body Light Mandible Material, Dental Impression Neck Needles Neoplasm Metastasis Normal Saline Periodontal Ligament phosphoric acid Physiologic Calcification physiology Plant Roots Polymerization Pulp Canals Radiography Resins, Plant Roentgen Rays Sealapex Silicones Steel Syringes Tooth Tooth Root Ultrasonics

Top products related to «Material, Dental Impression»

1
Universal testing machine by Instron
Sourced in United States, United Kingdom, Germany, Brazil, India, Canada, Spain
A universal testing machine is a device used to measure the force required to break, stretch, or compress a sample of material. It applies tensile, compressive, or shear stress to the sample and measures the resulting deformation. The core function of a universal testing machine is to perform standardized material tests to determine the mechanical properties of a wide range of materials.
2
Alginoplast by Kulzer
Sourced in Germany
Alginoplast is a lab equipment product manufactured by Kulzer. It is a precision alginate impression material used in dental applications. The core function of Alginoplast is to capture accurate impressions of patients' teeth and oral structures.
3
Impregum by 3M
Sourced in Germany, United States
Impregum is a polyether-based impression material used in dental procedures. It is designed to provide accurate and detailed impressions of the oral cavity, which are essential for the fabrication of dental prosthetics and restorations. Impregum offers a balanced viscosity and hydrophilic properties to ensure optimal reproduction of the dental structures.
4
Aquasil ultra lv by Dentsply
Sourced in Germany, United States
Aquasil Ultra LV is a low-viscosity impression material manufactured by Dentsply. It is designed for use in dental impression procedures.
5
Aquasil ultra xlv by Dentsply
Sourced in Germany
Aquasil Ultra XLV is a low-viscosity addition silicone impression material designed for use in dental laboratories. It is formulated to provide accurate and detailed impressions for dental applications.
6
Impregum penta by 3M
Sourced in Germany
Impregum Penta is a polyether-based impression material used in dentistry for taking impressions of teeth and oral structures. It is a two-part system that mixes a base and a catalyst to create a precise, dimensionally stable impression.
7
Impregum f by 3M
Sourced in Germany, Sao Tome and Principe
Impregum F is a polyether-based impression material designed for dental applications. It is a two-component system that includes a base paste and a catalyst paste. Impregum F is used to create accurate impressions of the oral cavity, which are then used to fabricate dental restorations such as crowns, bridges, and dentures.
8
Vh 7000 by Keyence
Sourced in Japan
The VH-7000 is a high-performance digital microscope designed for laboratory and industrial applications. It features a high-resolution camera and advanced image processing capabilities to capture detailed images and video of small-scale samples.
9
Reprosil by Dentsply
Sourced in United States
Reprosil is a silicone-based material designed for dental impressions. It is used to capture accurate replicas of teeth and supporting structures in the oral cavity.
10
Impregum soft by 3M
Sourced in United States, Germany
Impregum Soft is a polyether-based impression material used in dental procedures. It is designed to provide accurate and stable impressions for the creation of dental prosthetics.

More about "Material, Dental Impression"

Dental impression materials, also known as impression compounds or materials, are crucial components in the field of dentistry.
These substances are used to create a precise negative mold or imprint of a patient's teeth and surrounding oral structures.
The captured details are then utilized to fabricate customized dental prosthetics, such as crowns, bridges, dentures, and other restorations.
The most commonly used impression materials include silicones, alginates, and polyvinyl siloxanes (PVS).
Silicone-based materials, like Aquasil Ultra LV and Aquasil Ultra XLV, offer exceptional accuracy and dimensional stability.
Alginates, such as Alginoplast, are also widely employed due to their ease of use and affordability.
Polyvinyl siloxanes, including Impregum, Impregum Penta, and Impregum F, are renowned for their superior detail reproduction and resistance to distortion.
The selection of the appropriate impression material is crucial, as it directly affects the accuracy and fit of the final dental restoration.
Researchers continually work to optimize impression protocols, leveraging AI-driven comparisons to identify the best materials and techniques, such as the use of Universal testing machines to assess the physical properties of these materials.
Improving the reproducibility and accuracy of dental impression protocols is an ongoing challenge.
Solutions like PubCompare.ai, which utilizes AI to compare and identify the most effective impression materials and techniques, can enhance the quality of dental restorations and improve patient outcomes.
By exploring the latest advancements in dental impression materials, such as the high-performance materials Reprosil and VH-7000, dentists can ensure the precision and longevity of their patients' dental work.