A semi-digital bite force measuring device

Abstract

The utility model discloses a kind of semi-digitalization occlusal force measuring devices, including individualized curved surface sensing diaphragm and data acquisition module;Individualized curved surface sensing diaphragm is used to be placed into patient's mouth, adhere to dental surface anatomical form to gather stress signal in occlusion process, individualized curved surface sensing diaphragm includes ion gel dielectric layer, electrode circuit layer and TPU film packaging layer, ion gel dielectric layer is located between two electrode circuit layers, and each electrode circuit layer outer side is respectively covered with a layer of TPU film packaging layer;The output end of the electrode circuit layer of individualized curved surface sensing diaphragm is connected with data acquisition module by data line, and data acquisition module is used to receive the stress signal in occlusion process collected by individualized curved surface sensing diaphragm.The utility model solves the following problems existing in prior art: it is easy to cause mandibular position distortion when measuring, three-dimensional occlusal force information is lost, and the device is easy to be deformed, thereby affecting occlusal force data reliability.

Description

Technical Field

[0001] This utility model relates to a measuring device, and more particularly to a semi-digital bite force measuring device. Background Technology

[0002] In the field of oral diagnosis and treatment, orthodontic and prosthodontic procedures often require precise measurement of the patient's occlusal force to assess the occlusal relationship and guide the development of treatment plans. Semi-digital occlusal force measurement devices are key equipment for meeting this measurement requirement.

[0003] Existing semi-digital bite force measurement devices, represented by the T-Scan bite analyzer, mainly consist of a sensing diaphragm, a data acquisition handle, and a data cable. Its working principle is as follows: when bite force is applied to the sensing diaphragm, more than 1500 piezoresistors distributed on the diaphragm will change their resistance according to the applied force. After connecting the sensing diaphragm to a computer via the data cable, the accompanying software can convert the resistance changes at each sensing point into force changes and display them as charts or images on the software interface, thus achieving a visual presentation and data reading of bite force. This device has already been applied to some extent in clinical practice.

[0004] However, existing semi-digital occlusal force measurement devices, such as T-Scan, still have significant technical shortcomings, making it difficult to meet the demands for higher precision in diagnosis and treatment. The sensing diaphragm in existing devices has a planar structure. When the upper and lower jaws bite onto the planar sensing diaphragm, even if the diaphragm deforms to some extent, it still supports the cusps and fossae of the teeth. This structural characteristic not only easily leads to accidental slippage of the cusps, causing distortion of the mandibular position, but also results in the loss of some three-dimensional occlusal force information. Furthermore, repeated biting can cause minute permanent deformation of the sensor, affecting the accuracy of subsequent measurements. Although the sensing array on the existing sensing diaphragm consists of densely packed varistors, small non-sensing areas still exist between adjacent varistors. When the occlusal contact point happens to fall within these non-sensing areas, the force on the varistors around these non-sensing areas fluctuates, leading to inaccurate changes in the output resistance value and affecting the reliability of the occlusal force data. Utility Model Content

[0005] To address this issue, the present invention provides a semi-digital bite force measuring device, which solves the problems of mandibular position distortion, loss of three-dimensional bite force information, easy deformation of the device, and impact on the reliability of bite force data caused by existing technologies.

[0006] To achieve the above objectives, this utility model provides the following technical solution: a semi-digital bite force measuring device, comprising a personalized curved surface sensing diaphragm and a data acquisition module;

[0007] The personalized curved surface sensing membrane is used to be inserted into the patient's mouth and conform to the anatomical shape of the tooth surface to collect the force signal during the biting process. The personalized curved surface sensing membrane includes an ion gel dielectric layer, an electrode circuit layer and a TPU film encapsulation layer. The ion gel dielectric layer is located between two electrode circuit layers, and each electrode circuit layer is covered with a TPU film encapsulation layer.

[0008] The output terminal of the electrode circuit layer of the personalized curved surface sensing diaphragm is connected to the data acquisition module via a data line. The data acquisition module is used to receive the force signal acquired by the personalized curved surface sensing diaphragm during the biting process.

[0009] As a preferred embodiment of the semi-digital bite force measurement device, the personalized curved sensing diaphragm forms a five-layer stacked structure, which includes an outer TPU film encapsulation layer, an upper electrode circuit layer, an ion gel dielectric layer, a lower electrode circuit layer, and an inner TPU film encapsulation layer.

[0010] As a preferred embodiment of the semi-digital bite force measurement device, both the upper electrode circuit layer and the lower electrode circuit layer are made by printing gallium indium alloy conductive ink on a TPU film, and the electrodes of the upper electrode circuit layer and the lower electrode circuit layer correspond to the bite contact points in the patient's mouth.

[0011] As a preferred embodiment of the semi-digital bite force measuring device, the ionogel dielectric layer is an ultraviolet-curable ionogel, which covers the surface of the upper electrode circuit layer facing the lower electrode circuit layer and the surface of the lower electrode circuit layer facing the upper electrode circuit layer.

[0012] As a preferred embodiment of the semi-digital bite force measuring device, the output terminals of the upper electrode circuit layer and the lower electrode circuit layer are directly connected to the signal input terminal of the data acquisition module, and the data acquisition module is used to receive the capacitance signals transmitted by the upper electrode circuit layer and the lower electrode circuit layer.

[0013] As a preferred embodiment of a semi-digital bite force measurement device, the TPU film encapsulation layer enables the personalized curved sensing diaphragm to conform to the overall anatomical shape of the patient's teeth.

[0014] As a preferred embodiment of a semi-digital bite force measurement device, the number of electrodes in the electrode circuit layer is consistent with the number of bite contact points in the patient's mouth, and the electrode arrangement of the electrode circuit layer avoids non-sensing areas.

[0015] This utility model has the following advantages:

[0016] First, this invention uses a personalized curved sensing diaphragm that fits the anatomical shape of the patient's teeth, avoiding the problem of existing planar sensing diaphragms supporting the upper and lower cusp fossae, reducing the distortion of the mandibular position caused by accidental slippage of the cusps, reducing the risk of permanent deformation of the diaphragm, ensuring the accuracy of subsequent measurements, and reducing the loss of three-dimensional occlusal force information.

[0017] Secondly, the electrodes of the personalized curved sensing diaphragm correspond to the occlusal contact points in the patient's mouth, and the electrode arrangement avoids non-sensing areas. This avoids the problem of inaccurate data caused by force fluctuations in the surrounding piezoresistor when the occlusal contact point falls in a non-sensing area, thus improving the reliability of occlusal force data acquisition.

[0018] Third, the dielectric layer of the ionogel can generate capacitance changes when compressed. Combined with the electrode circuit layer, it can accurately collect the bite force signal. The signal is then received by the data acquisition module, providing accurate raw data for subsequent bite force analysis and helping doctors to more accurately judge the patient's bite condition.

[0019] Fourth, the personalized curved surface sensing diaphragm adopts a five-layer stacked structure. The TPU film encapsulation layer can protect the internal structure and ensure that the diaphragm fits the tooth surface, reducing the interference of the diaphragm on diagnosis and treatment during occlusion, and improving patient comfort and clinical convenience. Attached Figure Description

[0020] To more clearly illustrate the embodiments of this utility model or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings in the following description are merely exemplary, and those skilled in the art can derive other embodiments based on the provided drawings without creative effort.

[0021] The structures, proportions, sizes, etc. illustrated in this specification are only for the purpose of assisting those skilled in the art in understanding and reading the content disclosed herein, and are not intended to limit the implementation conditions of this utility model. Therefore, they have no substantial technical significance. Any modifications to the structure, changes in the proportional relationships, or adjustments to the size, without affecting the effects and purposes that this utility model can produce, should still fall within the scope of the technical content disclosed in this utility model.

[0022] Figure 1 This is a schematic diagram of a conventional T-Scan bite analyzer provided by this utility model;

[0023] Figure 2 This invention provides a schematic diagram of the bite analysis of a conventional T-Scan bite analyzer.

[0024] Figure 3A schematic diagram of the semi-digital bite force measuring device provided in this embodiment of the utility model;

[0025] Figure 4 A schematic diagram of the electrode circuit layer of the semi-digital bite force measuring device provided in this embodiment of the utility model;

[0026] Figure 5 A schematic diagram of the bite force measurement device provided in this embodiment of the utility model.

[0027] In the figure, 1 is a personalized curved surface sensing diaphragm; 2 is a data acquisition module; 11 is a TPU film encapsulation layer; 12 is an electrode circuit layer; 13 is an ion gel dielectric layer; 111 is an outer TPU film encapsulation layer; 121 is an upper electrode circuit layer; 122 is a lower electrode circuit layer; and 112 is an inner TPU film encapsulation layer. Detailed Implementation

[0028] The following specific embodiments illustrate the implementation of this utility model. Those skilled in the art can easily understand other advantages and effects of this utility model from the content disclosed in this specification. Obviously, the described embodiments are only some, not all, of the embodiments of this utility model. Based on the embodiments of this utility model, all other embodiments obtained by those skilled in the art without creative effort are within the protection scope of this utility model.

[0029] like Figure 1 As shown, the T-Scan bite analyzer inserts the gold fingers at the rear end of the sensing diaphragm a1 into the interface of the handle a2, and the pressure-sensitive resistor array a3 on the sensing diaphragm a1 is placed in the patient's mouth for biting; as... Figure 2 As shown, when in use, the sensing diaphragm a1 is placed between the patient's upper and lower teeth. The resistance change generated by each pressure-sensitive resistor a4 after being subjected to force can be converted into a force value by the corresponding software and displayed on the computer.

[0030] First, such as Figure 2 When the upper and lower jaws bite onto the planar sensor diaphragm, even if the diaphragm deforms to some extent, it still supports the cusps and fossae of the upper and lower teeth. This not only causes unexpected slippage of the cusps, leading to distortion of the mandibular position, but also results in the loss of some three-dimensional occlusal force information. Furthermore, it can cause minor permanent deformation of the sensor, affecting the accuracy of subsequent use. Secondly, as... Figure 1 Although the sensing array of the sensing diaphragm a1 is composed of dense varistors, there are small non-sensing areas between each varistor a4. When the contact point falls on these non-sensing areas, the force on the varistor around the non-sensing area will fluctuate, thus affecting the change in the output resistance value.

[0031] In view of this, the present invention provides a semi-digital bite force measuring device, which solves the problems of mandibular position distortion, loss of three-dimensional bite force information, and easy deformation in the prior art, thus affecting the reliability of bite force data. The following are the specific contents of the embodiments of the present invention.

[0032] See Figure 3 and Figure 4 This utility model provides a semi-digital occlusal force measurement device, including a personalized curved surface sensing diaphragm 1 and a data acquisition module 2. The personalized curved surface sensing diaphragm 1 is inserted into the patient's mouth and conforms to the anatomical shape of the tooth surface to collect force signals during the occlusal process. The personalized curved surface sensing diaphragm 1 includes an ion gel dielectric layer 13, an electrode circuit layer 12, and a TPU film encapsulation layer 11. The ion gel dielectric layer 13 is located between two electrode circuit layers 12, and each electrode circuit layer 12 is covered with a TPU film encapsulation layer 11. The output terminal of the electrode circuit layer 12 of the personalized curved surface sensing diaphragm 1 is connected to the data acquisition module 2 via a data line. The data acquisition module 2 is used to receive the force signals collected by the personalized curved surface sensing diaphragm 1 during the occlusal process.

[0033] Among them, the personalized curved sensing diaphragm 1, as a component that directly contacts the teeth, is designed to conform to the anatomical shape of the tooth surface, which can avoid the problem of existing planar diaphragms supporting the cusps and fossae, and reduce the distortion of the mandibular position; the ion gel dielectric layer 13 is located between the two electrode circuit layers 12. When the patient bites, the biting force acts on the diaphragm, causing the ion gel dielectric layer 13 to be compressed, its dielectric constant changes, and thus a capacitance change is generated. This change is captured by the electrode circuit layers 12 on both sides; the TPU film encapsulation layer 11 not only protects the internal electrodes and gel structure from the interference of the oral environment, but also adapts to the tooth surface morphology through shaping; the data line serves as a signal transmission channel, stably transmitting the capacitance signal collected by the electrode circuit layer 12 to the data acquisition module 2, ensuring that the signal is not lost.

[0034] In this embodiment, the personalized curved sensing diaphragm 1 forms a five-layer stacked structure, which includes an outer TPU film encapsulation layer 111, an upper electrode circuit layer 121, an ion gel dielectric layer 13, a lower electrode circuit layer 122, and an inner TPU film encapsulation layer 112.

[0035] Specifically, the five-layer stacked structure is an optimized design that achieves both functional and structural stability of the diaphragm. The outer TPU film encapsulation layer 111 and the inner TPU film encapsulation layer 112 form a double protective shell, wrapping the electrodes and gel layer in the middle from both sides. This not only prevents internal components from shifting or being damaged under biting pressure, but also ensures the fit between the diaphragm and the tooth surface through overall shaping. The upper electrode circuit layer 121 and the lower electrode circuit layer 122 are symmetrically distributed on both sides of the ionogel dielectric layer 13, allowing for simultaneous acquisition of capacitance change signals from both directions, reducing signal deviations that may occur with acquisition from a single direction. The ionogel dielectric layer 13 is located in the central core position, and its uniform distribution ensures the consistency of signals acquired by the upper and lower electrode layers. The tight integration of the five layers also reduces the risk of deformation of the diaphragm during use in the oral cavity, ensuring measurement accuracy.

[0036] In this embodiment, both the upper electrode circuit layer 121 and the lower electrode circuit layer 122 are printed on a TPU film using gallium indium alloy conductive ink, and the electrodes of the upper electrode circuit layer 121 and the lower electrode circuit layer 122 correspond to the biting contact points in the patient's mouth.

[0037] Specifically, gallium-indium alloy conductive ink possesses excellent conductivity and flexibility. When printed on TPU film, it can adapt to the tooth surface curve by shaping the TPU film, avoiding circuit breakage due to film bending and ensuring the stability of signal transmission. The design of the electrodes corresponding to the occlusal contact points is the key to solving the problem of data fluctuation in the non-sensoring area of ​​existing devices. After determining the occlusal contact points based on the patient's intraoral scanning data, the electrodes are precisely placed at these positions. When the patient bites, the occlusal force acts directly on the electrode, while the non-sensoring area does not have a direct occlusal force. This avoids signal errors caused by force fluctuations of the electrodes around the non-sensoring area and improves the accuracy of force signal acquisition at each contact point.

[0038] In this process, the virtual model of the maxilla after occlusion alignment is moved 100μm in the direction perpendicular to the occlusal plane using MeshLab software. The area where the upper and lower teeth overlap after staining is the occlusal contact point. Based on the marking results, a corresponding personalized electrode circuit is designed.

[0039] In this embodiment, the ion gel dielectric layer 13 is a UV-curable ion gel, which covers the surface of the upper electrode circuit layer 121 facing the lower electrode circuit layer 122 and the surface of the lower electrode circuit layer 122 facing the upper electrode circuit layer 121.

[0040] Specifically, UV-curable ionomer gels have the characteristics of fast curing speed and stable structure after curing. Through UV curing, a uniform dielectric layer can be quickly formed, and the cured gel is not easy to flow or deform under interlocking pressure, ensuring stable dielectric properties. The gel covers the opposing surfaces of the upper and lower electrode circuit layers 12, enabling the electrode layer and gel layer to form a complete electrode-gel-electrode capacitor structure. When the interlocking force is applied, the gel layer is compressed as a whole, and its contact area with the upper and lower electrodes and its own thickness change can be captured by the electrodes on both sides simultaneously, thereby generating a symmetrical and stable capacitance signal. This avoids signal differences caused by uneven gel coverage and ensures the reliability of force-to-electricity conversion.

[0041] In this embodiment, the output terminals of the upper electrode circuit layer 121 and the lower electrode circuit layer 122 are directly connected to the signal input terminal of the data acquisition module 2. The data acquisition module 2 is used to receive the capacitance signals transmitted by the upper electrode circuit layer 121 and the lower electrode circuit layer 122.

[0042] Specifically, the output terminals of the upper electrode circuit layer 121 and the lower electrode circuit layer 122 are directly connected to the data acquisition module 2, which reduces intermediate links in the signal transmission process and lowers the possibility of signal attenuation or interference. The data acquisition module 2 can synchronously receive the capacitance signals transmitted by the two electrode layers. By comparing the consistency of the two signals, it can be preliminarily judged whether the acquired signal is reliable. If the deviation between the two signals is small, it indicates that the biting force is uniform and the gel layer deformation is stable, and the signal is highly reliable. If the deviation is large, it can indicate that the membrane may have a positional shift or structural abnormality, which can be adjusted in time to ensure the accuracy of subsequent biting force analysis based on capacitance signals.

[0043] In this embodiment, the TPU film encapsulation layer 11 makes the personalized curved surface sensing membrane 1 fit the overall anatomical shape of the patient's tooth surface.

[0044] Specifically, the TPU film has good plasticity and elasticity. Through the shaping process, the encapsulation layer can be made into a curved structure that fits the concave and convex shape of the patient's tooth surface, thereby driving the electrode layer and gel layer inside the film to synchronously adhere to the tooth surface. This fitting design allows the film to deform slightly with the movement of the teeth during biting, rather than supporting the cusp and fossa like a flat film, thereby reducing accidental slippage of the cusps, avoiding distortion of the mandibular position, and at the same time ensuring that the biting force is evenly transmitted to the gel layer, ensuring that the force at each biting contact point can be accurately collected by the corresponding electrode, reducing the loss of force signal caused by the gap between the film and the tooth surface.

[0045] In this embodiment, the number of electrodes in the electrode circuit layer 12 is consistent with the number of occlusal contact points in the patient's mouth, and the electrode arrangement of the electrode circuit layer 12 avoids non-sensing areas.

[0046] Specifically, the number of electrodes matches the number of occlusal contact points, enabling "one-to-one" signal acquisition. This means that the force at each occlusal contact point is captured by a corresponding electrode, avoiding data confusion caused by multiple contact points sharing a single electrode. This allows physicians to clearly distinguish the specific force at each contact point. The electrodes are positioned to avoid non-sensing areas, where no electrodes are distributed. When an occlusal contact point falls within a pre-defined sensing area, there are no extra electrodes around it affected by the force at the non-contact point. This avoids resistance or capacitance changes caused by force fluctuations around electrodes in non-sensing areas, ensuring that the signal transmitted by each electrode corresponds only to the occlusal force at its contact point, thus improving the accuracy of data acquisition.

[0047] The method of using this utility model is as follows:

[0048] Preliminary preparation and membrane customization: Based on the patient's intraoral scan data, the virtual model of the maxilla after occlusion alignment was moved 100μm towards the occlusal direction in a direction perpendicular to the occlusal plane using MeshLab software. The overlapping area of ​​the upper and lower dentition was stained to determine the occlusal contact point. According to the position of the occlusal contact point, a customized electrode circuit was printed on a TPU film using gallium indium alloy conductive ink to form an upper electrode circuit layer 121 and a lower electrode circuit layer 122. UV-curable ionogel was applied to the opposing surfaces of the two electrode circuit layers 12, and then a TPU film encapsulation layer 11 was wrapped around the outside of the two electrode circuit layers 12 to form a five-layer stacked structure. Finally, the personalized curved surface sensing membrane 1 was shaped and encapsulated under vacuum pressure of 80kPa at 130℃.

[0049] Device connection and inspection: Connect the output terminal of the electrode circuit layer 12 of the customized curved surface sensing diaphragm 1 to the signal input terminal of the data acquisition module 2 through the data cable. Check whether the connection is stable and ensure that the data acquisition module 2 can receive the signal normally to avoid affecting subsequent measurements due to poor contact.

[0050] Diaphragm placement and positioning: Instruct the patient to maintain a comfortable sitting posture, gently place the personalized curved sensing diaphragm 1 into the patient's mouth, adjust the position of the diaphragm so that it conforms to the anatomical shape of the patient's teeth, ensure that the electrodes on the diaphragm accurately correspond to the occlusal contact points in the patient's mouth, and at the same time inform the patient to avoid moving their head or oral tissues at will.

[0051] Occlusion measurement and signal acquisition: The patient performs occlusal movements according to normal occlusal habits. At this time, the occlusal force is applied to the personalized curved surface sensing membrane 1, causing the ion gel dielectric layer 13 inside the membrane to be compressed and generate capacitance changes. The electrode circuit layer 12 captures the capacitance change signal and transmits the signal to the data acquisition module 2 in real time. The data acquisition module 2 synchronously receives the capacitance signals transmitted from the upper electrode circuit layer 121 and the lower electrode circuit layer 122.

[0052] Post-measurement operation and membrane processing: After the patient completes multiple biting actions (to ensure sufficient effective data is collected), instruct the patient to slowly open their mouth and gently remove the personalized curved surface sensing membrane 1 from the oral cavity; disconnect the data cable from the data acquisition module 2, clean the membrane or dispose of it according to medical waste regulations, and at the same time tidy up the data acquisition module 2 and the data cable to prepare for the next use.

[0053] See Figure 5 Based on each patient's specific situation, a sensor diaphragm is customized. The personalized diaphragm can not only fit perfectly and simulate the tooth surface morphology to a certain extent, reducing interference during the biting process, but also ensure that the biting contact point corresponds to the force sensing point on the diaphragm, reducing data fluctuations caused by biting in non-sensing areas. This allows for more accurate acquisition of the force at different biting contact points for physician analysis.

[0054] The present invention has been described in a relatively specific and detailed manner above through general description and specific embodiments. It should be understood that, based on the technical concept of the present invention, several conventional adjustments or further innovations can be made to these specific embodiments; however, as long as they do not depart from the technical concept of the present invention, the technical solutions obtained by these conventional adjustments or further innovations also fall within the protection scope of the claims of the present invention.

Claims

1. A semi-digital bite force measuring device, characterized in that, It includes a personalized curved surface sensing diaphragm (1) and a data acquisition module (2); The personalized curved surface sensing membrane (1) is used to be inserted into the patient's mouth and conform to the anatomical shape of the tooth surface to collect the force signal during the biting process. The personalized curved surface sensing membrane (1) includes an ion gel dielectric layer (13), an electrode circuit layer (12) and a TPU film encapsulation layer (11). The ion gel dielectric layer (13) is located between two electrode circuit layers (12), and each electrode circuit layer (12) is covered with a TPU film encapsulation layer (11). The output end of the electrode circuit layer (12) of the personalized curved surface sensing diaphragm (1) is connected to the data acquisition module (2) via a data line. The data acquisition module (2) is used to receive the force signal collected by the personalized curved surface sensing diaphragm (1) during the biting process.

2. The semi-digital bite force measuring device according to claim 1, characterized in that, The personalized curved sensing diaphragm (1) forms a five-layer stacked structure, which includes an outer TPU film encapsulation layer (111), an upper electrode circuit layer (121), an ion gel dielectric layer (13), a lower electrode circuit layer (122), and an inner TPU film encapsulation layer (112).

3. The semi-digital bite force measuring device according to claim 2, characterized in that, Both the upper electrode circuit layer (121) and the lower electrode circuit layer (122) are printed on a TPU film using gallium indium alloy conductive ink. The electrodes of the upper electrode circuit layer (121) and the lower electrode circuit layer (122) correspond to the biting contact points in the patient's mouth.

4. The semi-digital bite force measuring device according to claim 2, characterized in that, The ion gel dielectric layer (13) is a UV-curable ion gel, which covers the surface of the upper electrode circuit layer (121) facing the lower electrode circuit layer (122) and the surface of the lower electrode circuit layer (122) facing the upper electrode circuit layer (121).

5. The semi-digital bite force measuring device according to claim 2, characterized in that, The output terminals of the upper electrode circuit layer (121) and the lower electrode circuit layer (122) are directly connected to the signal input terminal of the data acquisition module (2). The data acquisition module (2) is used to receive the capacitance signals transmitted by the upper electrode circuit layer (121) and the lower electrode circuit layer (122).

6. The semi-digital bite force measuring device according to claim 1, characterized in that, The TPU film encapsulation layer (11) makes the personalized curved surface sensing membrane (1) fit the patient's tooth surface anatomy as a whole.

7. The semi-digital bite force measuring device according to claim 2, characterized in that, The number of electrodes in the electrode circuit layer (12) is consistent with the number of occlusal contact points in the patient's mouth, and the electrode arrangement of the electrode circuit layer (12) avoids non-sensing areas.

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