Ankle-Foot System with an Energy Storing Keel, Vertical Shock Absorbing Pylon, Active Dorsiflexion and Axial Rotation

Abstract

Embodiments can relate to a prosthetic foot system. The system can include an ankle joint housing co-locating a rotation sub-assembly, a torsional shock absorbing sub-assembly, and a vertical shock absorbing sub-assembly. The system can include a foot component attached to the ankle joint housing. The system can be configured as a co-designed architecture to functionally integrate at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

Claims

1. A prosthetic foot system, comprising: an ankle joint housing co-locating a rotation sub-assembly, a torsional shock absorbing sub-assembly, and a vertical shock absorbing sub-assembly; and a foot component attached to the ankle joint housing; wherein the prosthetic foot system is configured as a co-designed architecture to functionally integrate at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

2. The prosthetic foot system of claim 1, wherein: the multi-axial motion includes dorsiflexion motion, plantarflexion motion, and/or sagittal rotation.

3. The prosthetic foot system of claim 1, wherein: the ankle joint housing provides multi-axial motion with stiffness modulation in single gait cycle in concert with the foot component providing inversion, eversion, plantar-flexing, and dorsi-flexing.

4. The prosthetic foot system of claim 3, wherein: the dorsiflexion motion range is between 0 degree and 7 degrees; the plantarflexion motion range is between 0 degrees and 5 degrees; and the sagittal rotation range is between 0 degrees and 16 degrees.

5. A prosthetic foot system, comprising: a shock absorbing sub-assembly including an energy storing keel and a vertical loading pylon; an axial rotational sub-assembly attached to the shock absorbing sub-assembly; a heel component attached to the energy storing keel; and an extension rod; wherein the shock absorbing sub-assembly and axial rotational sub-assembly are interconnected via the extension rod; and wherein the prosthetic foot system is configured as a co-designed architecture to functionally integrate at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

6. The prosthetic foot system of claim 5, wherein: the energy storing keel is J-shaped.

7. The prosthetic foot system of claim 5, further comprising: a shock absorbing bumper is disposed between the heel component and the energy storing keel.

8. The prosthetic foot system of claim 5, wherein: the axial rotational sub-assembly includes plural torsional springs configured to provide non-linear stiffness as rotation of the axial rotational sub-assembly occurs.

9. The prosthetic foot system of claim 8, wherein: the plural torsional springs includes a first tortional spring, a second tortional spring, and a third tortional spring; and the first tortional spring has a stiffness (S1), the second tortional spring has a stiffness (S2), and the third tortional spring has a stiffness (S3), wherein S1>S2>S3.

10. The prosthetic foot system of claim 9, wherein: the plural torsional springs includes plural cut-outs configured to engaged with the extension rod.

11. The prosthetic foot system of claim 10, wherein: the first tortional spring has a first cut-out, the second tortional spring has a second cut-out, and the third tortional spring has a third cut-out; and the first cut-out, the second cut-out, and the third cut-out are configured to facilitate selective engagement of the first tortional spring, the second tortional spring, and the third tortional spring, respectively, with the extension rod.

12. The prosthetic foot system of claim 11, wherein: the extension rod has a cross-sectional shape; the plural cut-outs each have a profile that corresponds to the cross-sectional shape; the first cut-out's profile complements the cross-sectional shape to a first degree (D1), the second cut-out's profile complements the cross-sectional shape to a second degree (D2), and the third cut-out's profile complements the cross-sectional shape to a third degree (D3); and D1>D2>D3.

13. The prosthetic foot system of claim 12, wherein: the extension rod's cross-sectional shape is square; the first cut-out's profile is square; the second cut-out's profile is a concave quadrilateral with a curved side; the third cut-out's profile is a concave quadrilateral with a curved side; and a degree of concavity for the curved side of the third cut-out is greater than a degree of concavity for the curved side of the second cut-out.

14. The prosthetic foot system of claim 9, wherein: the plural torsional springs includes: plural cut-outs configured to engaged with the extension rod, each individual cut-out being formed in a central portion of an individual tortional spring; and plural spiral shaped cut-outs configured to facilitate axial rotation of the axial rotational sub-assembly, each individual spiral shaped cut-out being formed in a peripheral portion of an individual tortional spring.

15. A method for functionally integrating ambulatory functions of a prosthetic foot system comprising: an ankle joint housing including a rotation sub-assembly, a torsional shock absorbing sub-assembly, and a vertical shock absorbing sub-assembly; and a foot component attached to the ankle joint housing, the method comprising: causing at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

16. A method for providing ambulation via a prosthetic foot system comprising: an integrated ankle joint housing including a rotation sub-assembly, a torsional shock absorbing sub-assembly, and a vertical shock absorbing sub-assembly; and a foot component; and wherein: the integrated ankle joint housing is attached to the foot component; the integrated ankle joint housing is configured to provide multi-axial motion; and the foot component is configured to invert, evert, plantar-flex, and dorsi-flex, the method comprising: during ambulation: deflecting and storing energy during an initial gait stage of a gait phase; and releasing energy during a subsequent gait stage of the gait phase.

17. The method of claim 16, further comprising: during ambulation: providing dynamic stiffness within and/or between a swing phase, a stance phase, a toe off phase, a mid swing phase, a midstance phase, a terminal stance phase, an early flatfoot phase, a loading response phase, a pre swing phase, a swing phase, a gait phase, and a late swing phase.

18. The method of claim 16, further comprising: during ambulation: providing differential axial rotation.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0042] The above and other objects, aspects, features, advantages and possible applications of the present innovation will be more apparent from the following more particular description thereof, presented in conjunction with the following drawings. Like reference numbers used in the drawings may identify like components.

[0043] FIGS. 1a and 1b show the design philosophy of the innovation and the prior art, respectively.

[0044] FIG. 2 is a high-level side cross-sectional view of one preferred embodiment revealing how the components can be intelligently co-located and integrated.

[0045] FIG. 3 is a high-level side cross-sectional view of another preferred embodiment revealing how the components can be intelligently co-located and integrated.

[0046] FIG. 4 is an isometric perspective view of the preferred embodiment from FIG. 2.

[0047] FIG. 5 is a top perspective view of the preferred embodiment from FIG. 2.

[0048] FIG. 6 is an exploded isometric perspective view of the preferred embodiment form FIG. 2.

[0049] FIG. 7 is a front cross-sectional view of the preferred embodiment from FIG. 2.

[0050] FIG. 8 compares the shock absorber in an uncompressed due to no load state, 8a, and compressed due to vertical body load state, 8b.

[0051] FIG. 9 compares the sagittal rotation of the device when either no load is applied or a dorsiflexion load is applied 9a, and when a plantarflexion load is applied 9b.

[0052] FIG. 10 compares one of the torsional springs when a medial axial load is applied 10a, no axial load is applied 10b, and when a lateral axial load is applied 10c.

[0053] FIG. 11 compares the physical state of the device when a medial axial load is applied 11a, no axial load is applied 11b, and when a lateral axial load is applied 11c.

[0054] FIG. 12 compares the cutouts on each of the three torsional springs in FIGS. 12a, 12b, and 12c.

[0055] FIG. 13 shows the state of the device during swing phase, where the vertical shock absorber is uncompressed, active dorsiflexion causes the foot to be dorsiflexed, and the axial rotation angle is at zero degrees.

[0056] FIG. 14 shows the state of the device during an example heel strike, where the vertical shock absorber is slightly compressed, the foot is plantarflexed, and the axial rotation angle is medially rotated.

[0057] FIG. 15 shows the state of the device during an example mid-stance to toe-off, where the vertical shock absorber is significantly compressed, the foot is dorsiflexed, and the axial rotation angle is laterally rotated.

DETAILED DESCRIPTION OF THE INVENTION

[0058] The following description is of exemplary embodiments that are presently contemplated for carrying out the present invention. This description is not to be taken in a limiting sense, but is made merely for the purpose of describing the general principles and features of the present invention. The scope of the present invention is not limited by this description.

[0059] This innovation relates to GoraliPaa SFT, a foot-ankle system comprising of an energy-storing keel, an integrated shock absorbing pylon, an articulating ankle component that enables multi-axial motion with stiffness modulation in single gait cycle and active dorsi-flexion during swing phase, and a torsional component that enables ab/ad-duction. It is intended to be used with a cosmetic foot shell.

[0060] The embodiments contain 3 distinct functionalities, and all the components are integrated as a single product via a singular ankle joint housing 2. In FIGS. 4, 5, 6, and 7, relating to embodiment 1, the prosthetic foot system 6 contains an energy storing J-shaped keel 13 that is integrated with a vertical loading pylon 14 to as part of shock absorption sub-assembly 3. A heel component 15 is attached to the J-shaped keel section 13 along with an elastomer bumper 16 via one or more fasteners such as rivet 17 to form the prosthetic foot system 6. The vertical loading pylon 14 allows a controlled motion for shock absorption of up to 10 millimeters of vertical displacement via an extension rod 15 and a shock absorbing compression spring 16. The extension rod 15 may be attached to the vertical loading pylon 14 via a fastener such as set screw 17. To bind the shock absorbing assembly 3 to the ankle joint housing 2, a hole 18 in the extension rod 15 can utilize a cotter pin 19. The length of the assembly is calculated such that there is a small amount of pre-load to keep the assembly taut even when no body load is applied by the user. The heel component 15 has a length such that it allows for an aesthetic foot shell cover to be attached. Additional elastomeric components may be used such as Sandwich 20, rod bumper 21, and pin bumper 22 to prevent metallic components from scraping one another to avoid noise or scratches. The ankle joint housing 2 allows for multi-axial motion with stiffness modulation in single gait cycle. During the transition from stance phase to swing phase of ambulation, and throughout the duration of the swing phase, the dorsiflexion angle is actively increased without the user's input. This actively induced dorsiflexion angle is 7 degrees (measured from neutral). Additionally, during the stance phase, plantarflexion is allowed up to 5 degrees (measured from neutral) for a total range of motion of 12 degrees. The sagittal rotation is accomplished via a pin and hole connection from a pair of connectors 23 and 24 to ankle joint housing 2. Additionally, the active dorsiflexion is enabled via an elastomeric spring 25 with notches that allow it to attach to the spring holder 26. The bottom of the elastomeric spring 25 is then trapped between spring holder 26 and the top of the connecter 23 such that it will not come loose. The spring holder 26 may be fastened to the ankle joint housing 2 via one or more fasteners such as countersunk screw 27, along with an aesthetic cover 28. Additional components and features provide boundary conditions to limit the motion and prevent noise such as plantar bumper 29, bottom bumper 30, overload protector 31, and overload bumper 32. The overload bumper 32 may be fastened to the ankle joint via a countersunk screw 27 along with an aesthetic cover 28. The prosthetic foot system 6 can be attached to the ankle joint 2 via one or more fasteners 33 and aesthetic covers 34. Additionally, elastomeric bearings 35 can be placed between the connectors 23 and 24 and the ankle joint 2 to further prevent scraping. An axial rotational sub-assembly 5 allows vertical twisting motion between the foot and pelvis during ambulation. This medial and lateral rotation is up to 15 degrees each (from neutral), for a total range of motion of 30 degrees. This sub-assembly could consist of one or more spring members 36, 37, and 38, each separated by an elastomeric piece 39, 40, and 41 to prevent scraping. A cutout in the middle of the components allows for the aforementioned extension rod 15 to pass through and connect the entire assembly within one concentric, co-located component.

[0061] The patient's body load and initial heel strike impulse causes the shock absorber 16 to compress vertically, absorbing the shock of the initial stage of stance phase starting from initial heel-strike. The vertical loading pylon enables controlled motion by displacing up to 10 millimeters (patient load/impulse dependent) to provide shock absorbing functionality. This motion is achieved in this embodiment via a polyester and rubber blend compression spring. FIG. 8a, relating to embodiment 1, shows the device's physical state with no load applied, such as in swing phase. This leads to a fully uncompressed pylon state 42. FIG. 8b, relating to embodiment 1, shows the device's physical state with body load applied, such as in initial heel strike to stance phase. With sufficient body lead, this leads to a partially or fully compressed pylon state 43. When body load and initial heel strike impulse are applied, the shock absorber 16 compresses to allow the controlled motion. A J-shaped, energy storing keel 13 is present. The keel is able to invert/evert and plantar/dorsi-flex when the relevant body load is applied. The device's keel can be made of carbon fiber composite, a material widely used in industry for its energy storing properties. Upon load application starting from heel strike, the keel will bend like a spring, and during toe push off transitioning into swing phase, the keel will release the stored energy to return to its original shape.

[0062] The device contains an articulating ankle joint component 2 that provides multi-axial motion with stiffness modulation in single gait cycle. This component's holes rotate around the pin joints on symmetrical lateral connectors 23 and 24. It utilizes a pair of symmetrical rotating pin and hole connectors. The device utilizes a sponge-like elastomeric structure 25 that functions as a compliant spring such that at transition of stance phase to swing phase, the product will increase the ankle's dorsiflexion angle and maintain it throughout swing phase. This component is easily overpowered by body weight and compresses during stance phase to allow plantarflexion. FIG. 9a, relating to embodiment 1, illustrates the device in a dorsiflexion state 44 of 7, and FIG. 9b, relating to embodiment 1, illustrates the device in a plantarflexion state 45 of 5. During swing phase, the dorsiflexion is actively enforced by the elastomeric spring 25. The TPU spring will also, due to its interaction with body load, automatically adjust the heel height/angle and range of motion to accommodate the patient's shoe selection. Further manual adjustment of the range of motion and heel height is also available via choosing an elastomeric spring that is of the desired density/size which will change the mechanical characteristics such as stiffness, allowable range of motion, and default dorsiflexion angle. The articulating component exhibits non-linear stiffness in the sagittal plane. The elastomeric spring 25 enforcing dorsiflexion is very weak and easy to overpower by body load during initial heel strike. However, towards the end of stance phase as toe-push off begins to occur and the dorsiflexion reaches its maximum and the keel 13 bends under load, the overload protector 31 engages against the keel 13 and causes the articulating ankle joint 2 to exhibit relatively high stiffness to allow for a stable and strong toe-push off. Additionally, this stiffener significantly shortens the effective cantilever length of the keel 13, which significantly increases its stiffness dynamically.

[0063] The device contains an axial rotation sub-assembly 5 that allows for vertical twisting motion between the foot and pelvis during ambulation. The axial rotation sub-assembly could consist of 3 stacked torsional springs each separated by noise cancelling elastomer to form an overall sandwich type component. FIG. 10, related to embodiment 1, illustrates the concept of the axial rotation via one of the torsional springs 36, with FIG. 10a representing axial deformation due to medial load, FIG. 10b representing no axial deformation due to no axial load, and FIG. 10c representing axial deformation due to lateral load. When medial or lateral force is applied, the springs enable the patient's leg to be rotated relative to the keel. Each of the torsional springs has a jutted key 46, which mates with a slot in the ankle joint 2 to control and restrain the motion. Because these are springs, they will return to neutral as in FIG. 10b, 0 degrees of rotation, when no load is applied, typically during swing phase. When the prosthetic foot system 6 is in stance phase, the axial rotation sub-assembly is allowed to rotate independently of the foot, allowing for vertical twisting motion between the foot system 6 and pylon 14. In FIG. 11, related to embodiment 1, FIG. 11a shows the device in a state of medial rotation 47, FIG. 11b shows the device in a state of no axial rotation 48, and FIG. 11c shows the device in a state of lateral axial rotation 49. The rotation shown is 15 degrees in the medial and lateral directions (from neutral), for a total range of motion of 30 degrees. The torsional springs exhibit differential, non-linear stiffness, that is, it will require more force to go from 14 to 15 than from 0 to 1 of rotation measured from neutral. This is due to the structural nature of the torsional springs themselves, as well as the variable engagement of the torsional springs. The first torsional spring can be made the tallest, and therefore the stiffest, while subsequent torsional springs can be made smaller. This will let additional torsional springs add stiffness while not increasing it dramatically to an uncomfortable level for the patient. The first torsional spring 36 has a tighter cutout than subsequent ones which would have more and more hourglass shaped cutouts to modulate the stiffness appropriately. In the presented embodiment, key breakpoints at 5 and 10 (in either direction) will cause a different number of torsional springs to engage, which will modulate the stiffness to higher values as the angle of rotation increases. The first torsion spring 36 has a feature such that it is always engaged in force application towards neutral. From 0 to 5 measured from neutral (in either direction), it is the only spring engaged, and the rotational stiffness is the lowest. The second torsion spring 37 has a feature such that it is engaged from 5 onwards in either direction from neutral. From 5 to 10 measured from neutral (in either direction), the first and second torsion springs 36 and 37 are engaged and the rotational stiffness is increased. The third torsion spring 38 has a feature such that it is engaged from 10 onwards in either direction from neutral. All of the torsion springs 36, 37, and 38 are engaged at 10 to 15 (in either direction), and the rotational stiffness is at its highest. FIG. 12 reveals how the concentric cutout for the extension rod 15 can be manufactured in a particular shape to allow this non-linearity. The first torsion spring 36 in FIG. 12a has a relatively square cutout 50 and will always be in contact with the extension rod 15 as it rotates. The second torsion spring 37 in FIG. 12b has a mildly hourglass shaped cutout 51 and will only be in contact with the extension rod 15 after it rotates a prescribed amount. The third torsion spring 38 in FIG. 12c, has the most hour-glass shaped cutout 52, and any subsequent springs can have more and more hourglass shaped cutouts such that they will only engage in stiffness modulation after a certain rotational angle is reached, making the stiffness dynamic. The spiral shaped cutout 53 in each of the springs 36, 37, and 38 enables the axial rotation when load is applied medially or laterally.

[0064] All of the aforementioned functionalities can be activated simultaneously or asynchronously depending on the state of the forces being applied on the foot. FIG. 13, relating to embodiment 1, shows the swing phase state of the foot 54, where the sagittal rotation is in dorsiflexion, the vertical loading pylon is not compressed, and the axial rotation is at neutral, or zero degrees. FIG. 14, relating to embodiment 1, shows one example of an initial heel strike scenario 55, where, due to the ground reaction force being applied primarily at the heel, the sagittal rotation is in plantarflexion, the vertical loading pylon has a small amount of initial compression, and some medial axial rotation is present. FIG. 15, relating to embodiment 1, shows an example of a scenario 56 between mid-stance and toe-off, where, due to the ground reaction force being applied primarily at the toe, the sagittal rotation is in dorsiflexion, the vertical loading pylon has a large amount of compression, and some lateral axial rotation is present. Once toe-off has occurred, and the foot is in the air without any ground reaction forces, it will return to the state 54.

[0065] As can be appreciated, embodiments can relate to a prosthetic foot system. The prosthetic foot system can include an ankle joint housing. The ankle joint housing can be configured for co-locating a rotation sub-assembly, a torsional shock absorbing sub-assembly, and/or a vertical shock absorbing sub-assembly. The prosthetic foot system can include a foot component. The foot component can be attached to the ankle joint housing. The prosthetic foot system can be configured as a co-designed architecture. For instance, the prosthetic foot system can be configured to functionally integrate at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion (e.g., dorsiflexion motion, plantarflexion motion, and/or sagittal rotation) with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption. This can be achieved by the interaction of the rotation sub-assembly, a torsional shock absorbing sub-assembly, and/or a vertical shock absorbing sub-assembly causing at least two of the said functions to operate in concert. The concerted action is described in detail above. An exemplary concerted action can involve the ankle joint housing providing multi-axial motion with stiffness modulation in single gait cycle in concert with the foot component providing inversion, eversion, plantar-flexing, and/or dorsi-flexing. Embodiments can provide dorsiflexion motion range between 0 degree and 7 degrees, plantarflexion motion range between 0 degrees and 5 degrees, and sagittal rotation range between 0 degrees and 16 degrees.

[0066] An exemplary embodiment of the prosthetic foot system can include a shock absorbing sub-assembly. The shock absorbing sub-assembly can include an energy storing keel and a vertical loading pylon. The prosthetic foot system can include an axial rotational sub-assembly attached to the shock absorbing sub-assembly. The prosthetic foot system can include a heel component attached to the energy storing keel. In some embodiments, the energy storing keel can be J-shaped. In some embodiments, a shock absorbing bumper can be disposed between the heel component and the energy storing keel. The shock absorbing sub-assembly and axial rotational sub-assembly can be interconnected via the extension rod to facilitate a co-locating, co-designed architecture which functionally integrates at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

[0067] One of the aspects that facilitates the co-designed architecture and the concerted functionality, is a torsional spring arrangement. For instance, the axial rotational sub-assembly can include plural torsional springs. The plural torsional springs can be configured to provide non-linear stiffness as rotation of the axial rotational sub-assembly occurs. In an exemplary embodiment, the plural torsional springs can include a first tortional spring, a second tortional spring, and a third tortional spring. More or less torsional springs can be used. With the exemplary embodiment, the first tortional spring can have a stiffness (S1), the second tortional spring can have a stiffness (S2), and the third tortional spring can have a stiffness (S3). It is contemplated for S1>S2>S3. This can be achieved by the plural torsional springs including plural cut-outs configured to engaged with the extension rod. (See, e.g., FIGS. 10 and 12). For instance, the first tortional spring can have a first cut-out, the second tortional spring can have a second cut-out, and the third tortional spring can have a third cut-out. The first cut-out, the second cut-out, and the third cut-out can be configured to facilitate selective engagement of the first tortional spring, the second tortional spring, and the third tortional spring, respectively, with the extension rod.

[0068] The extension rod has a cross-sectional shape. The plural cut-outs each can have a profile that corresponds to the cross-sectional shape. For instance, the first cut-out's profile can complement the cross-sectional shape to a first degree (D1). The second cut-out's profile can complement the cross-sectional shape to a second degree (D2). The third cut-out's profile can complement the cross-sectional shape to a third degree (D3). It is contemplated for D1>D2>D3. In an exemplary embodiment, the extension rod's cross-sectional shape is square, the first cut-out's profile is square, the second cut-out's profile is a concave quadrilateral with a curved side, and the third cut-out's profile is a concave quadrilateral with a curved side. A degree of concavity for the curved side of the third cut-out is greater than a degree of concavity for the curved side of the second cut-out.

[0069] The plural torsional springs can include plural cut-outs configured to engaged with the extension rod, wherein each individual cut-out can be formed in a central portion of an individual tortional spring. In addition, plural spiral shaped cut-outs can be formed and configured to facilitate axial rotation of the axial rotational sub-assembly, wherein each individual spiral shaped cut-out can be formed in a peripheral portion of an individual tortional spring.

[0070] As can be appreciated, embodiments can relate to a method for functionally integrating ambulatory functions of a prosthetic foot system. The method can involve using an embodiment of the prosthetic foot system can causing at least two functions of: (i) torsional shock absorption, (ii) multi-axial motion with stiffness modulation in single gait cycle, (iii) active dorsiflexion, and (iv) vertical shock absorption by causing the at least two functions to operate in concert.

[0071] Embodiments can also relate to providing ambulation via a prosthetic foot system. The method can involve using an embodiment of the prosthetic foot system and, during ambulation, deflecting and storing energy during an initial gait stage of a gait phase. The method can further involve releasing energy during a subsequent gait stage of the gait phase. The method can further involve providing dynamic stiffness within and/or between a swing phase, a stance phase, a toe off phase, a mid swing phase, a midstance phase, a terminal stance phase, an early flatfoot phase, a loading response phase, a pre swing phase, a swing phase, a gait phase, and a late swing phase. The method can further involve providing differential axial rotation.

[0072] It should be understood that the disclosure of a range of values is a disclosure of every numerical value within that range, including the end points. It should also be appreciated that some components, features, and/or configurations may be described in connection with only one particular embodiment, but these same components, features, and/or configurations can be applied or used with many other embodiments and should be considered applicable to the other embodiments, unless stated otherwise or unless such a component, feature, and/or configuration is technically impossible to use with the other embodiment. Thus, the components, features, and/or configurations of the various embodiments can be combined together in any manner and such combinations are expressly contemplated and disclosed by this statement.

[0073] It will be apparent to those skilled in the art that numerous modifications and variations of the described examples and embodiments are possible considering the above teachings of the disclosure. The disclosed examples and embodiments are presented for purposes of illustration only. Other alternate embodiments may include some or all of the features disclosed herein. Therefore, it is the intent to cover all such modifications and alternate embodiments as may come within the true scope of this invention, which is to be given the full breadth thereof.

[0074] It should be understood that modifications to the embodiments disclosed herein can be made to meet a particular set of design criteria. Therefore, while certain exemplary embodiments of the systems, compositions, materials, apparatuses, and methods of using and making the same disclosed herein have been discussed and illustrated, it is to be distinctly understood that the invention is not limited thereto but may be otherwise variously embodied and practiced within the scope of the following claims.