A method of measuring tooth mobility

A61C19/045 -

The invention relates to dentistry, can be used to diagnose supporting and retaining apparatus of the tooth or tissue surrounding the implant. The method comprises the application to the tooth of the lower jaw two variables force with constant amplitude but different frequencies. The frequency of the second variable force

is in the range of 1.5 to 2.5 frequency

the first variable force. Measure the amplitude X and

offset teeth for both variables forces. Define

. The parameter R is judged on the state of the restraint apparatus of the tooth of the lower jaw. The technical result - improving the quality and accuracy of diagnosis, reducing measurement error. 1 C. p. F.-ly, 4 Il., 3 table.

The invention relates to dentistry, can be used to diagnose supporting and retaining apparatus of the tooth or tissue surrounding the implant.

There is a method of determining the mobility of a tooth by applying to the tooth a variable force, providing the reciprocating oscillation of the tooth, and measuring the amplitude of displacement of the tooth (Author sweetersacrifice tissues supporting and retaining apparatus of the tooth, defined by the value of mobility of the tooth. The method has low accuracy and does not improve the quality of diagnosis, because the total mobility of the tooth is not always realistically reflects the pathological changes occurring in pornodive the apparatus of the tooth in various diseases.

The closest is the way of measuring the mobility of a tooth, comprising the application to the tooth variable force constant amplitude and frequency, providing a reciprocating oscillation of the tooth below the frequencies of the tooth, the measurement of the amplitude of the displacement of the tooth (Patent of Russian Federation №2065724, And 61 In 5/05 And 61 With 19/04, publ. 1996).

In addition, in this method, the measurement of the amplitude of the displacement of the tooth is produced with the separation of these two components, respectively in-phase variable power and shifted in phase relative to it at 90 degrees, the magnitude of which is judged elastic and viscous characteristics of the mobility of the tooth. These components are carriers of valuable information about the condition of the periodontium. The measurement method was implemented in a portable two-parameter periodontally used in clinical practice.

The advantages of this method are: additional infochange of this method is the complexity of diagnosing the state of the retaining device of the teeth of the lower jaw, because of her own mobility, which is different for each individual. In practical implementations for the lower jaw of this method used to measure the mobility of the tooth in the physiological norm for a particular patient, that has not always been possible due to the lack of teeth in the same norm with him, or to fix the position of the lower jaw pliers, and then compare the mobility of the tooth to the average indicator of the same tooth in the norm, which generally reduces the accuracy of the diagnosis. As will be seen later, the introduction of fixtures does not allow to significantly improve the quality of diagnostics. When measuring components of the amplitude-phase variable power and shifted in phase relative to it at 90 degrees, the diagnosis was further worsened due to errors made in the measurements of proper mobility of the jaw.

Solved by the invention the task is to enhance the functionality and tools to diagnose the nature of the disorders of the restraint apparatus of the tooth of the lower jaw, improving the reliability of results and implementation of the rapid assessment of the state of uderjivaya the AI method, - improving the quality and accuracy of diagnosis, reducing measurement errors.

To solve the problem with the achievement of the technical result in the known method of measuring the mobility of a tooth, comprising the application to the tooth of a variable force F₁constant amplitude a and frequency

providing a reciprocating oscillation of the tooth below the frequencies of the tooth, the measurement of the amplitude of the X displacement of the tooth, according to the invention for the teeth of the lower jaw after application to the tooth mentioned variable force F₁make application to him of the second variable force F₂with the same constant amplitude And, as for the mentioned variable force F₁but with different frequency

equal to 1.5 to 2.5

frequency mentioned variable force F₁also providing reciprocating oscillation of the tooth below the frequencies of the tooth, measure the amplitude of the X displacement of the tooth when the second variable force F₂determine the parameter R in accordance with the mathematical expression

and the parameter R is judged on the state of the holding is consistent with, to measure the amplitude of displacement of a tooth with said variable force during the second variable force produced with the separation of the two components, respectively in-phase alternating forces and shifted in phase relative to them by 90 degrees, the magnitude of which is judged elastic and viscous characteristics of the mobility of the tooth.

These advantages, and features of the present invention are explained best option for its implementation with reference to the accompanying drawings.

Fig.1 depicts a dynamic model of supporting and retaining apparatus of the tooth, the teeth of the upper jaw;

Fig.2 - same for the teeth in the lower jaw.

Fig.3 - the same, the updated model.

Fig.4 - physical model of the lower jaw, schematically.

In clinical studies of tooth mobility with a healthy periodontium, it was found that the mobility of the same teeth in the upper and lower jaws differ markedly. This effect is due to an error caused by the fact that the lower jaw, due to the small mass of her tissue is not completely fixed, but moves together with the tooth. Experimental confirmation of this was the reduction of this error with increasing frequency variable (periodic) force F.

With the following, the movement of the upper jaw is much less than the natural (resonant) displacement of the tooth on the frequency of the current variable power more than 80 Hz.

The error of measurement of tooth mobility depends on the frequency of non-monotonic. On the one hand, measurement error in the mobility of the teeth of the lower jaw decreases with increasing frequency. On the other hand, from a certain frequency, impact measurement begins to influence the mass of the tooth and closer to the resonant frequency of the system the tooth - periodontal - bone this effect becomes predominant. This restriction does not reduce the error to an acceptable value only by increasing the frequency of the variable force F. Systematization of experimental data found no significant errors in the elastic component, but the residual error of the viscous component of the mobility was comparable with the magnitude of the mobility of the tooth with a healthy periodontium. In this variation of this error on different teeth were small, which allowed us to introduce a correction of the results of measurement of tooth mobility of the lower jaw by simply subtracting the average error.

Despite the fact that the correction of the results was possible to obtain more reliable clinical results, raglani, extend the range reliably measured mobility of the teeth of the lower jaw.

To understand the factors affecting the accuracy of measurement of tooth mobility and estimation of the magnitude of this error, you must create a realistic dynamic model of the tooth. The initial part of the study was the choice of the dynamic model of the mechanical system of the tooth - periodontal tissue of the lower jaw on the basis of experimental data. Was created a computer program for the numerical simulation, to simulate oscillations of mechanical systems, modify the parameters of these systems, including the number of elements of these systems, the parameters influencing variable power and display the simulation results in a visual form.

The complexity of the model leads to an increase in the number of unknown parameters, direct measurement of which in vivo is almost an impossible task. As a result of comparison of the results of clinical experiments and numerical simulations, it was found that the dynamic characteristics of the teeth of the upper jaw for frequencies above 80 Hz satisfactorily describes the simplest dynamic viscoelastic model with the same mass m, the elastic element with stiffness k and a viscous eleia was defined by, in the dynamic model of the lower jaw teeth, you need to enter additional items.

Introduction to the model instead of rigid supports additional mass M (Fig.2), similar in weight to the weight of the lower jaw (the mass of the bone and surrounding soft tissue), allows you to play in the dynamic model of amplitude-phase empirical relationships. Introduction to model various additional elements, in principle, should serve to further Refine the model and improve the accuracy of coincidence of the results of simulation and clinical studies. But, as shown by experimental studies to obtain a remarkable effect is not possible, as the model (Fig.2) reproduces the experiment with an accuracy comparable with the accuracy of this experiment. However, the introduction of additional viscous element, a₀(Fig.3), representing the viscosity of the surrounding lower jaw soft tissues, several clarifies the dynamic model (the value of a few percent match data). The magnitude of the viscous forces exerted by the element a₀(Fig.3) too small and for practical calculations good approximation is the model (Fig.2).

When measuring tooth mobility of the claimed method can be used, n is the phase offset between tooth x and affecting force F. The differential equation describing the model (Fig.1)

where a is the complex amplitude of the force F=AEⁱ

^t,

f is the circular frequency, x=Xeⁱ

^t- the offset of the tooth, m is the mass of a tooth, and is the damping ratio of the viscous element and k is the stiffness of the system, the tooth - periodontal - bone.

This allows to Express the unknown a and k using known parameters obtained in the measurement result. These expressions are written in complex form

Error

²m, depending on the mass of a tooth, the solution of equation (2) can be made small by reducing the frequency

. However, there are limitations on the decrease - increase the error of measurement of the displacement x as the frequency decreases due to the influence of the lower jaw.

The mobility of the lower jaw not only introduces error in the measurement of tooth mobility, but does not allow to compensate for the error caused by the variation of mass of teeth.

The transition to the model (Fig.2) for the mandible leads to the following system of differential equations:

For the model (Fig.3) the system of equations looks

The amplitude of the tooth and the jaw X’ is a complex value, that is, each consists of two parameters. The number of equations for complicated models has doubled, but the number of unknown real parameters of the system (3) and (4) exceeds the number of equations respectively two and three, which makes it impossible to obtain only the solutions of these equations. Simultaneous measurement of X’ (missing two real parameters) in the measurement of X could, in principle, to bring the system (3) to the system with a unique solution. However, from the above equations it is not clear whether this extra dimension to practically implement.

At first glance after process modeling mechanical systems the tooth-periodontal tissue of the lower jaw, the situation looks a dead-end and there are no solutions to the problem of determining the mobility of the teeth of the lower jaw.

However, if you spend an extra dimension at a frequency of

that is different from frequencies

the system (3) will complement the analogue of equations And, X

and

- known parameters, and m, M, X’

’ and k is unknown. The system (5) formally has only one solution. In contrast to equation (1) it is nonlinear because it contains a multiplicative members, i.e., works of unknown. Mathematical expression (5) is a system of equations that has no solution in quadratures. However, using the symmetry of the system leads to its relatively simple approximate solutions.

Model (Fig.3) you can also cause the system with a unique solution. The evaluation shows that the accuracy of measurement of tooth mobility using the appropriate algorithm increases slightly, but significantly complicate the measurement process and increases the complexity of the solution of nonlinear systems of high order.

Multiplying each of the equations so that the first terms of the equations turned out to be pairwise equal, we get

pairwise subtracting equations, exclude m and M

The difference of these equations

after conversion privateline part will provide expressions for the variables of interest

The mathematical expression (6) are not a complete solution, because the right side contains the unknown X' and

If we consider that the displacement of the lower jaw X' and

absolute value is much smaller displacement of the tooth X and

you can obtain an approximate solution

The algorithm described by formula (7), it is easier to analyze after simple transformations

Force acting on the jaw, almost equal to the force acting on the tooth. The displacement of the mass (in our case the jaws under the influence of this force is inversely proportional to the square of the frequency. Then the contribution of the mass of the jaw in

²X and

the same and the difference in brackets (7') will be significantly less dependent on the mass. Multiplier

required for normalization of the result.

If the frequencies are too close to each other, there is a risk of a sharp HC is observed in this expression. Therefore, it is necessary to make the frequency difference is big enough, otherwise the result of the application of the algorithm can be negative. On the other hand, with increasing frequency affecting force offset jaw will decrease and compensating the effect of the application of algorithm (7) will decrease accordingly. Studies have shown that the best result from the application of algorithm (7) and the implementation of the method is achieved if the frequency

is within 150-250%

To implement the method was created measuring system of the portable personal computer (notebook). The system includes: measuring probe, a laptop, a PCMCIA card ADC (analog-to-digital Converter) and a specially designed electronic unit that includes a tunable filter harmonics generator and the instrumental amplifier.

The system is as follows.

The software part of the system runs after contact of the probe with the test tooth. The program initializes the timer Board ADC, which generates a binary signal is strictly a given frequency. Tunable filter harmonics generator retains all harmonics of this signal, preobtained signal into force of the F₁acting on the tooth. Movement (vibration) of the tooth are perceived piezoelectric accelerometer and after amplification instrument amplifiers are returned on Board ADC. 12-bit ADC simultaneously converts the signal generator and the accelerometer into digital form and stores them in RAM. Next, from these data by means of digital filtering are two components of the signal generator and amplifier H. the Entire cycle is repeated at a second frequency F₂. And thus, we get the full data set to apply the algorithm (7).

The final values of the two component mobility elastic and viscous components p and q are calculated using the values of two component stiffness

where

- the loss angle.

Note that the loss angle

proportional to the square of the periodontium, which gives the option of an independent value for the diagnosis of diseases that were known from the closest analogue.

In the system of measurement of tooth mobility has the ability to automatically save the resulting data. There is also an additional possibility ion battery, the method is applicable for systems providing measurement and the total mobility of the teeth without extracting components, respectively in-phase alternating forces and shifted in phase relative to them by 90 degrees, because the main contribution to the error of measurement for the lower jaw makes a measurement error of the viscous component. However, she makes the most significant contribution to the error of the experimental data to measure the mobility and without separating the components.

For the experimental study of the algorithm was specially designed physical model of the lower jaw with floating support (Fig.4).

The physical model consists of two main units - the upper (movable) reference node 1 and the lower (stationary) node 2. On the upper node 1 is the set of elements simulating the teeth with various visco-elastic characteristics. Models of the teeth are steel rods 3, in the lower part of which is a package of thin disk springs 4. Package of disk springs 4 are immersed in the holes 5, filled with high-viscosity silicone fluid. Experimentally it was found that this design is most similar in mechanical properties to the real tooth. Several cones 6, rigidly attached to verneomrade 7, being in a compressed state due to the pull-up rope 8 nuts 9. This design allows you to change the degree of connection of movable and fixed parts of the model in a fairly wide range.

Studies using this physical model showed that the algorithm is resistant to the effect of changes in the mobility support of the lower jaw.

Thus, the claimed method is implemented as follows:

is applied to the tooth variable force F₁constant amplitude a and frequency

providing a reciprocating oscillation of the tooth below the frequencies of the tooth, measure the amplitude of displacement of the tooth's teeth in the upper and lower jaws (the value judge about changes supporting and retaining apparatus of the tooth of the upper jaw in comparison with the amplitude of displacement X in the physiological norm);

- then for the teeth of the lower jaw is applied to the tooth of the second variable force F₂with the same amplitude As that for the above-mentioned variable force F₁but with different frequency

measure the amplitude

displacement of the tooth;

- define

proportional skretny selected frequencies

and

which is judged on the state of the restraint apparatus of the tooth. To do this, compare the parameter R parameter R_Nfrom this same formula for the same tooth of the lower or upper jaw in the physiological norm. Formula

obtained by transforming the formula (7) for the amplitudes of X and

tooth mobility, given that k in the mathematical expression (7) is the rigidity, i.e., a value inversely proportional to the mobility.

In addition, if necessary, distinguish two components of the mobility of the elastic and viscous components of p₁and q₁and the elastic and viscous components of p₂and q₂at a frequency of

for a variable force F₁same teeth of the upper and lower jaws, respectively, and the elastic and viscous components

and

at a frequency of

for a variable force F₂at the second frequency for the lower jaw. Components p₁and

phase alternating forces F₁and F₂and the components of q₁and

shifted in phase by 90

) using the formula

and R_q(q₂and

) using the formula

The value of the parameters R_pand R_qjudge elastic and viscous characteristics of the mobility of the tooth of the mandible compared with parameters R_pNR_qNfrom this same formula for the same tooth of the lower and/or upper jaw in the physiological norm.

It is clear that when implementing the inventive method of measuring tooth mobility tests and measurements of the teeth for the upper jaw, including pathology or physiological norm, may not be conducted after sufficient set of statistics. Such measurements on the teeth of the upper jaw only serve to confirm the correctness of the measurements. Scope of the present invention is defined in independent claim, and professionals it is clear that the claimed method can be applied, additional improvements that do not alter the substance of this method. For example, the experts it is clear that to increase the accuracy of the measurement can be performed not only on two, but on several different frequencies.

OS is using the above described equipment for two frequencies

=100 Hz and

First measure the parameters of the amplitudes of displacement of a tooth of the upper jaw, under normal physiological N. Then measure the parameters of shear displacements same tooth of the lower jaw, under physiological norm. Then determine the parameters of the tooth with violation of the restraint apparatus of the tooth to the upper jaw. Determine the amplitude of the displacement of the same tooth of the lower jaw with the same violations (defined radiographically) supporting and retaining device. The measurement results are summarized in table.1.

As can be seen from the measurement results, the parameters of the amplitude of the displacement of the tooth depending on the frequency of the upper jaw does not change. For the lower jaw of the amplitude change in the direction of its increase. The difference of the parameters calculated by the formula

for the same tooth in the normal lower jaw (X

)_N=30 μm/H, which corresponds to the value of X_N=30 μm/H in the upper jaw. In case of the same disease of the holding apparatus for the same teeth of the upper and lower jaws of the difference calculated by the same formula, when pathology (X

Example 2

The method is carried out analogously to example 1 at two frequencies

=150 Hz and

The measurement results are summarized in table.2.

As can be seen from the table.2, with increasing frequency parameters of the amplitudes of displacement of a tooth of the lower jaw a little closer to the values of offset same tooth of the lower jaw, but still very different from them. At the same time for a tooth of the upper jaw, which is in the physiological norm (X)_Nand

calculated according to the formula parameter R=30,6.

For the lower teeth with pathological changes supporting and retaining apparatus

based on the selected frequency equal to 70.9 μm/H, i.e., approximately equal to the amplitude of displacement of the tooth of the upper jaw in the pathology of X_P=70 μm/H.

Thus, the measurement of the amplitudes of the X and

displacement of the tooth with a variable force F₁and when the second variable force F₂with respectively selected from the interval cha is to exclude the impact of the lower jaw to the definition of pathology.

Example 3

The method is carried out analogously to example 1 at two frequencies

=100 Hz and

with the release of the elastic and viscous components of p and q. The measurement results are shown in table.3.

As follows from the table.3, the above correlation is stored at the division of the amplitude of displacement at the elastic and viscous components. Indeed, for a tooth of the lower jaw in normal physiological p₂(100) and

substituting in the formula

40 μm/H and 30 μm/N, we obtain R_p=26,7 μm/H, which is equal for the same tooth in normal physiological upper jaw relevant parameters

Accordingly, for a tooth in the physiological norm of the mandible q₂(100) and

equal to 30 μm/H and 20 μm/H. Calculating by the formula

we obtain R_q=16,7 μm/H. This value of R_qis equal to the magnitude of the viscous component for the same tooth in normal physiological upper jaw

For teeth with changes in supporting and retaining apparatus of the tooth of the lower jaw p₂(100)and

respectively 120 μm/H there

for a tooth of the upper jaw, and q₂and

and 50 μm/H. Calculating according to the formula given frequency

and

we obtain R_q=36,7 μm/H. I.e., the calculated value of R_qfor a tooth of the lower jaw corresponds exactly to the same parameter of the tooth of the upper jaw

when pathology.

As the experiments showed, there may be some minor discrepancies in the measured parameters. This, apparently, is connected with the practical impossibility of finding two of the same teeth in the upper and lower jaws with equivalent violations of their supporting and retaining device. But as follows from the studies and the data presented in table.1-3, the claimed method virtually eliminates the effect of mobility of the mandible and surrounding soft tissues, as well as the influence of individual differences masses lower jaws to each patient or examination.

Clinical study of the method of measuring tooth mobility has demonstrated the ability to measure the mobility of both the upper and lower jaw. The experimental data showed that the measurement accuracy is increased and the revealed way of measuring tooth mobility can be industrially applicable in dentistry for operational diagnostics of supporting and retaining apparatus of the tooth or tissue, surrounding the implant.

Claims

1. The method of measuring the mobility of a tooth, comprising the application to the tooth of a variable force F_1,constant amplitude a and frequency

providing a reciprocating oscillation of the tooth below the frequencies of the tooth, the measurement of the amplitude X of displacement of teeth, wherein the teeth of the lower jaw after application to the tooth mentioned variable force F₁make application to him of the second variable force F₂with the same constant amplitude As that for the above-mentioned variable force F₁but with different frequency

equal to 1,5

2,5

also providing reciprocating oscillation of the tooth below the frequencies of the tooth, measure the amplitude

displacement of the tooth when the second variable force F₂determine the parameter R in accordance with the mathematical expression

and the parameter R is judged on the state of the restraint apparatus of the tooth to the jaw.

2. The method according to p. 1, characterized in that the measurement of the amplitudes of the X and

, the largest of which is judged elastic and viscous characteristics of the mobility of the tooth.

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Device for monitoring chewing movements (versions) and earphone // 2504330

FIELD: medicine.

SUBSTANCE: invention relates to medical equipment, namely to devices for examination of human body movement. In the first version device is made with possibility of installation on user's head in the area of its temporal and/or masticatory muscles and includes Hall sensor, at least, one permanent magnet, installed with possibility of mutual displacement in resiliently deformable case, and unit of control and information processing. In the second version device is provided with resilient arc, by means of which resiliently deformable case is pressed to user's head. Earphone for monitoring chewing movements in addition to Hall sensor, at least, one permanent magnet, installed in resiliently deformable case with possibility of mutual displacement in case of its resilient deformation, contains unit of control and information processing, connected with loudspeaker.

EFFECT: application of the invention makes it possible to increase quality of filtration of mechanical fluctuations, induced by chewing movements, at the background of other fluctuations.

17 cl, 9 dwg

Method of determining prosthetic plane projection on person's face and device for its realisation // 2504345

FIELD: medicine.

SUBSTANCE: group of inventions relates to medicine, namely to dentistry, and is intended for determination of prosthetic plane projection on person's face. For this purpose device for registration of sagittal articular way, containing U-like shaped arc, passing from the area of temporo-mandibular joints to central maxillary incisors, is used. In the area of maxillary incisors arc is provided with paraocclusion fork. On each side of the arc, opposite the area of location of lower jaw joint, placed is one holder of registering device, made with possibility of contact with fixed on patient's face self-adhering millimetre paper. To find prosthetic plane projection on patient's face, Frankfurt horizontal line and line of lower jaw base are applied. Value of the first angle, formed by intersection of said lines, is determined. After that, by means of the claimed device determined is line of sagittal articular way, which together with line, representing prosthetic plane projection on patient's face, constitutes the second angle. Prosthetic plane projection on face is determined by formula: value of the second angle minus 102° equals value of the first angle.

EFFECT: method makes it possible to increase accuracy of prosthetic plane determination in form of its projection on patient's face due to application of dependence of 2 angles, where the first angle is formed by line of Frankfurt horizontal and line of lower jaw base, and the second angle by line of sagittal articular way and line representing prosthetic plane projection.

2 cl, 4 dwg

Method of sparing prosthetics with adhesive half-crowns // 2508069

FIELD: medicine.

SUBSTANCE: invention relates to dentistry and is intended for application in orthopedic and therapeutic dentistry. Gypsum models of patient's jaws are made. Biomechanics of lower patient's jaw movements is studied. Angles of sagittal and transversal joint paths of patient are determined. Obtained values are marked on scale of joint units of articulator, which imitates individual movements of patient's lower jaw. Gypsum models are placed in claimed apparatus and ceramic thin half-crowns are modelled on them under constant control of interaction of dentitions and articulation contacts, proper to patient. Preparation of teeth before application of prosthesis according to method includes grounding off sharp enamel crests and processing teeth surface by airbrasive machine with powder with size 50 mcm under pressure 20 atm until dull surface of enamel appears.

EFFECT: method makes it possible to reduce trauma and preserve viability of teeth with prosthetic appliance due to elimination of preparation of hard tissues of said teeth.

2 dwg, 1 ex

Method of upper jaw position spatial transfer taking into account individual parameters, occlusal yoke with determination of spatial position and device for upper jaw model spatial positioning for said method implementation // 2602044

FIELD: manufacturing technology.

SUBSTANCE: group of inventions includes occlusive yoke with determination of spatial position, device for upper jaw model spatial positioning and method of upper jaw position spatial transfer taking into account individual patient's parameters, refers to prosthetic dentistry and can be used for precise clinically determined properly upper jaw model positioning in articulator. Occlusal yoke with spatial position determination represents plate, used for evaluation of upper jaw denture occlusal plane topography. Plate is made with intraoral part in form of U-shaped element, bearing distal portions and equipped with handle, which is plate proximal part, bearing yoke positioning indicator relative to upper jaw denture along middle-sagittal line. Occlusal yoke is equipped with position determining sensor, arranged on plate proximal part. Yoke positioning indicator relative to upper jaw denture is made in form of projection or recess on plate surface in section between said sensor arrangement point and U-shaped plate element made with recording material retention facilities for teeth impression, gums and palatal surface.

EFFECT: invention increases accuracy of upper jaw location in articulator relative to articulator joint mechanism, considered as human maxillo-temporal joint.

11 cl, 6 dwg