Patent Publication Number: US-2018028811-A1

Title: Intelligent modularization

Description:
BACKGROUND 
     Hearing loss is generally of two types, conductive and sensorineural. Sensorineural hearing loss is due to the absence or destruction of the cochlear hair cells which transduce sound into nerve impulses. Various hearing prostheses have been developed to provide individuals suffering from sensorineural hearing loss with the ability to perceive sound. For example, cochlear implants have an electrode assembly which is implanted in the cochlea. In operation, electrical stimuli are delivered to the auditory nerve via the electrode assembly, thereby bypassing the inoperative hair cells to cause a hearing percept. 
     Conductive hearing loss occurs when the natural mechanical pathways that provide sound in the form of mechanical energy to cochlea are impeded, for example, by damage to the ossicular chain or ear canal. For a variety of reasons, such individuals are typically not candidates for a cochlear implant. Rather, individuals suffering from conductive hearing loss typically receive an acoustic hearing aid. Hearing aids rely on principles of air conduction to transmit acoustic signals to the cochlea. In particular, hearing aids amplify received sound and transmit the amplified sound into the ear canal. This amplified sound reaches the cochlea in the form of mechanical energy, causing motion of the perilymph and stimulation of the auditory nerve. 
     Unfortunately, not all individuals suffering from conductive hearing loss are able to derive suitable benefit from hearing aids. For example, some individuals are prone to chronic inflammation or infection of the ear canal. Other individuals have a malformed or absent outer ear and/or ear canals resulting from a birth defect, or as a result of medical conditions such as Treacher Collins syndrome or Microtia. 
     For these and other individuals, another type of hearing prosthesis has been developed in recent years. This hearing prosthesis, commonly referred to as a middle ear implant, converts received sound into a mechanical force that is applied to the ossicular chain or directly to the cochlea via an actuator implanted in or adjacent to the middle ear cavity. 
     SUMMARY 
     In accordance with an exemplary embodiment, there is an implantable device, comprising an implantable module including a first functional component, the implantable module being configured to effectively differentiate between a plurality of different second modules respectively placeable into signal communication with the module. 
     In accordance with another exemplary embodiment, there is a method comprising operating an implantable component as part of a partially implantable prosthesis based on a first received signal received by the implantable component, and automatically operating the implantable component as part of a fully implantable prosthesis based on a second received signal received by the implantable component. 
     In accordance with an exemplary embodiment, there is an implantable system, comprising a first implantable module having a first role in the implantable system, wherein the first implantable module is configured to adopt a second role automatically upon a changed circumstance. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Embodiments are described below with reference to the attached drawings, in which: 
         FIG. 1  is a perspective view of an ear system of a recipient; 
         FIG. 2A  is a perspective view of an exemplary hearing prosthesis in which at least some of the teachings detailed herein are applicable; 
         FIG. 2B  is a perspective view of another exemplary hearing prosthesis in which at least some of the teachings detailed herein are applicable; 
         FIG. 3  is a perspective view of an exemplary implantable component of an exemplary hearing prosthesis in which at least some teachings detailed herein are applicable; 
         FIG. 4  is a perspective view of a component of the implantable component of  FIG. 3 ; 
         FIG. 5  is a perspective view of an exemplary external component of an exemplary hearing prosthesis in which at least some teachings detailed herein are applicable; 
         FIG. 6  is a perspective view of an exemplary implantable system according to an exemplary embodiment; 
         FIG. 7  is a perspective view of another exemplary implantable system according to an exemplary embodiment; 
         FIG. 8  is a perspective view of another exemplary implantable system according to an exemplary embodiment; 
         FIG. 9  is a perspective view of another exemplary implantable system according to an exemplary embodiment; 
         FIG. 10  is a perspective view of another exemplary prosthesis according to an exemplary embodiment; 
         FIG. 11  is a perspective view of another exemplary implantable system according to an exemplary embodiment; 
         FIGS. 12-23  are functional block diagrams representing various exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 24A  depicts a functional block diagram of an exemplary system according to an exemplary embodiment with logic details and memory details; 
         FIG. 24B  depicts a functional block diagram of an exemplary system according to an exemplary embodiment with logic details and memory details; 
         FIG. 25  is a functional block diagram representing an exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 26  depicts a functional block diagram of the prosthesis of  FIG. 25 ; 
         FIG. 27  is a functional block diagram representing an exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 28  depicts a functional block diagram of the prosthesis of  FIG. 26 ; 
         FIGS. 29-33  are functional block diagrams representing various exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 34  is a perspective view of an exemplary implantable system according to an exemplary embodiment; 
         FIGS. 35-36  are functional block diagrams representing various exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 37  depicts a functional block diagram of an exemplary system according to an exemplary embodiment with logic details and memory details; 
         FIG. 38  are functional block diagrams representing various exemplary hearing prostheses according to some of the teachings detailed herein modularized format; 
         FIG. 39  depicts a functional block diagram of an exemplary system according to an exemplary embodiment with logic details and memory details; 
         FIG. 40  is a perspective view of an exemplary implantable system according to an exemplary embodiment; 
         FIG. 41  is a functional block diagram representing an exemplary hearing prostheses according to some of the teachings detailed herein in modularized format; 
         FIG. 42  depicts a functional block diagram of an exemplary system according to an exemplary embodiment with logic details and memory details; 
         FIG. 43  depicts a flowchart for an exemplary method according to an exemplary embodiment; and 
         FIG. 44  depicts another flowchart for another exemplary method according to an exemplary embodiment. 
     
    
    
     DETAILED DESCRIPTION 
       FIG. 1  is a perspective view of a human skull showing the anatomy of the human ear. As shown in  FIG. 1 , the human ear comprises an outer ear  101 , a middle ear  105 , and an inner ear  107 . In a fully functional ear, outer ear  101  comprises an auricle  110  and an ear canal  102 . An acoustic pressure or sound wave  103  is collected by auricle  110  and channeled into and through ear canal  102 . Disposed across the distal end of ear canal  102  is a tympanic membrane  104  which vibrates in response to sound wave  103 . This vibration is coupled to oval window or fenestra ovalis  112 , which is adjacent round window  121 . This vibration is coupled through three bones of middle ear  105 , collectively referred to as the ossicles  106  and comprising the malleus  108 , the incus  109 , and the stapes  111 . Bones  108 ,  109 , and  111  of middle ear  105  serve to filter and amplify sound wave  103 , causing oval window  112  to articulate, or vibrate in response to the vibration of tympanic membrane  104 . This vibration sets up waves of fluid motion of the perilymph within cochlea  140 . Such fluid motion, in turn, activates hair cells (not shown) inside cochlea  140 . Activation of the hair cells causes nerve impulses to be generated and transferred through the spiral ganglion cells (not shown) and auditory nerve  114  to the brain (also not shown) where they cause a hearing percept. 
     As shown in  FIG. 1 , semicircular canals  125  are three half-circular, interconnected tubes located adjacent cochlea  140 . Vestibule  129  provides fluid communication between semicircular canals  125  and cochlea  140 . The three canals are the horizontal semicircular canal  126 , the posterior semicircular canal  127 , and the superior semicircular canal  128 . The canals  126 ,  127 , and  128  are aligned approximately orthogonally to one another. Specifically, horizontal canal  126  is aligned roughly horizontally in the head, while the superior  128  and posterior canals  127  are aligned roughly at a 45 degree angle to a vertical through the center of the individual&#39;s head. 
     Each canal is filled with a fluid called endolymph and contains a motion sensor with tiny hairs (not shown) whose ends are embedded in a gelatinous structure called the cupula (also not shown). As the orientation of the skull changes, the endolymph is forced into different sections of the canals. The hairs detect when the endolymph passes thereby, and a signal is then sent to the brain. Using these hair cells, horizontal canal  126  detects horizontal head movements, while the superior  128  and posterior  127  canals detect vertical head movements. 
       FIG. 2A  is a perspective view of an exemplary direct acoustic cochlear stimulator  200 A in accordance with an exemplary embodiment. Direct acoustic cochlear stimulator  200 A comprises an external component  242  that is directly or indirectly attached to the body of the recipient, and an internal component  244 A that is temporarily or permanently implanted in the recipient. External component  242  typically comprises two or more sound input elements, such as microphones  224  for detecting sound, a sound processing unit  226 , a power source (not shown), and an external transmitter unit  225 . External transmitter unit  225  comprises an external coil (not shown). Sound processing unit  226  processes the output of microphones  224  and generates encoded data signals which are provided to external transmitter unit  225 . For ease of illustration, sound processing unit  226  is shown detached from the recipient. 
     Internal component  244 A comprises an internal receiver/transmitter unit (hereinafter referred to as a communications unit)  232  including an inductance coil portion  236  (which is made, in some embodiments, out of silicone in which platinum coils (not shown) are embedded) and a stimulator unit  220 , and a stimulation arrangement  250 A in electrical communication with stimulator unit  220  via cable  218  extending through artificial passageway  219  in mastoid bone  221 . Internal communications unit  232  and stimulator unit  220  are hermetically sealed within a biocompatible housing, and are sometimes collectively referred to as a stimulator/communications unit. 
     Internal communications unit  232  comprises an internal coil (not shown), and optionally, a magnet (also not shown) fixed relative to the internal coil. The external coil transmits electrical signals (i.e., power and stimulation data) to the internal coil via a radio frequency (RF) link. The internal coil is typically a wire antenna coil comprised of multiple turns of electrically insulated platinum or gold wire. The electrical insulation of the internal coil is provided by a flexible silicone molding (not shown). In use, implantable communications unit  232  is positioned in a recess of the temporal bone adjacent auricle  110 . 
     In the illustrative embodiment of  FIG. 2A , ossicles  106  have been explanted. However, it should be appreciated that stimulation arrangement  250 A may be implanted without disturbing ossicles  106 . 
     Stimulation arrangement  250 A comprises an actuator  240 , a middle ear prosthesis  252 A and a coupling element  251 A which includes an artificial incus  261 B (represented in a quasi-functional manner—some additional details of these components are described below). Actuator  240  is coupled to mastoid bone  221  so as to be held in the interior of artificial passageway  219  formed in mastoid bone  221 . 
     In this embodiment, stimulation arrangement  250 A is implanted and/or configured such that a portion of middle ear prosthesis  252 A abuts the round window  121 . In an alternate embodiment, the middle ear prosthesis  252 A can abut the oval window (not shown). In some alternate embodiments, stimulation arrangement  250 B may alternatively be implanted such that the middle ear prosthesis  252 A abuts an opening in horizontal semicircular canal  126 , in posterior semicircular canal  127  or in superior semicircular canal  128 . Any attachment regime that can enable a hearing percept to be evoked utilizing the stimulation arrangement  250 A can be utilized. 
     As noted above, a sound signal is received by microphone(s)  224 , processed by sound processing unit  226 , and transmitted as encoded data signals to internal communications  232 . Based on these received signals, stimulator unit  220  (sometimes referred to herein as a driver or driver unit) generates drive signals which cause actuation of actuator  240 . The mechanical motion of actuator  240  is transferred to middle ear prosthesis  252 A such that a wave of fluid motion is generated in the perilymph in the scala tympani of the cochlea. Such fluid motion, in turn, activates the hair cells of the organ of  Corti . Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (not shown) and auditory nerve  114  to cause a hearing percept in the brain. 
       FIG. 2B  depicts an exemplary embodiment of a middle ear implant  200 B having a stimulation arrangement  250 B comprising actuator  240  and a coupling element  251 B. Coupling element  251 B includes an ossicular replacement prosthesis or middle ear prosthesis  252 B and an artificial incus  261 B which couples the actuator to the middle ear prosthesis. In this embodiment, middle ear prosthesis  252 B abuts stapes  111 . 
       FIG. 3  is a perspective view of an exemplary internal component  344  of a middle ear implant in the form of a direct extra cochlear acoustic stimulator according to an exemplary embodiment. Internal component  344  comprises an internal communications unit  332 , a stimulator unit  320 , a stimulation arrangement  350 , and an actuator positioning mechanism  370 . As shown, communications unit  332  comprises an internal coil (not shown), and in some embodiments, a magnet  321  fixed relative to the internal coil. Internal communications unit  332  and stimulator unit  320  are typically hermetically sealed within a biocompatible housing. This housing has been omitted from  FIG. 3  for ease of illustration, and hence the end of the actuator positioning mechanism  370 , discussed in more detail below, which connects to the housing, is depicted with broken lines. Collectively, the internal communications unit  332 , the stimulator unit  320  and the housing form an implant body  345 . 
     Stimulator unit  320  is connected to stimulation arrangement  350  via a cable  328 . Stimulation arrangement  350  comprises an actuator  340 , a middle ear prosthesis  354 , and a coupling element  353 . A distal end of middle ear prosthesis  354  is configured to be positioned in one or more of the configurations noted above with respect to  FIGS. 2A-2B . A proximal end of middle ear prosthesis  354  is connected to actuator  340  via coupling element  353  and the distal end of the prosthesis is directly or indirectly coupled to the cochlea. In operation, actuator  340  vibrates middle ear prosthesis  354 . The vibration of middle ear prosthesis  354  generates waves of fluid motion of the perilymph, thereby activating the hair cells of the organ of  Corti . Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells and auditory nerve  114 . 
     Middle ear implant internal component  344  further includes actuator positioning mechanism  370 . As may be seen, actuator positioning mechanism  370  is connected to and extends from implantable body  345  and is configured to removably receive actuator  340 . 
       FIG. 4  depicts actuator positioning mechanism  470  as comprising two sub-components: extension arm  471  and extension arm  475 . Sub-component  471  includes arm  472  which is an integral part of housing  446  (where the cross-hatching of housing  446  seen in  FIG. 4  corresponds to the wall of the housing, as will be described in greater detail below). In an exemplary embodiment, arm  472  may be part of the same casting forming at least part of housing  446  (i.e., the arm  472  and at least a portion of the housing  446  form a monolithic component), although in an alternate exemplary embodiment, arm  472  may be a separate component that is attached to the housing  446  (e.g., via laser welding). In an exemplary embodiment, the casting may be made partially or totally out of titanium. In this regard, it is noted that the actuator support mechanism may be made partially or totally out of titanium, and the housing  446  may be made out of a different material. Sub-component  471  also includes flange  473  which forms a female portion of ball joint  474 . In this regard, sub-component  475  includes the male portion of the ball joint  474 , in the form of a ball  476 , as may be seen. Ball joint  474  permits the ball  476  of sub-component  475  to move within the female portion, thereby permitting sub-component  475  to articulate relative to sub-component  471 , and thus permitting actuator  340  to likewise articulate relative to middle ear implant internal component  344 . 
     Ball joint  474  enables the actuator  340  to be positioned at an adjustably fixed location relative to the implantable body  345 . In an exemplary embodiment, the ball joint  474  permits the location of the actuator  340  to be adjustable relative to the implant body in two degrees of freedom, represented by arrows  1  and  2  (first and second degrees of freedom, respectively), in  FIGS. 3 and 4 , although in some embodiments the joint may permit the location of the actuator  340  to be adjustable relative to the implant body in only one degree of freedom or in more than two degrees of freedom. 
     While actuator positioning mechanism  470  is depicted with a ball joint  474 , other types of joints may be utilized. By way of example, the joint may comprise a malleable portion of a structural component of the actuator positioning mechanism  470  that permits the actuator  340  to be positioned, as just detailed or variations thereof. In an exemplary embodiment, the joint is an elastically deformable portion or plastically deformable portion, or is a combination of elastically deformable and plastically deformable portions so as to enable the adjustment of the location of the received actuator relative to the implant body in the at least one degree of freedom. 
     As noted above, actuator positioning mechanism  470  further includes sub-component  475 . Sub-component  475  comprises ball  476  of ball joint  474 , arm  477 , trolley  478 , and actuator support  479 . Actuator support  479  is depicted as being in the form of a collar, and receives and otherwise holds actuator  340  therein, and thus holds the actuator  340  to the actuator positioning mechanism  470 . 
     The collar has an exterior surface  479 A and an interior surface  479 B, configured to receive actuator  340 . The interior diameter of the collar, formed by interior surface  479 B is approximately the same as the outer diameter of the cylindrical body of actuator  340 . The outer diameter of the collar, formed by exterior surface  479 A, is sized such that the collar will fit into the artificial passageway  219 . The length of the collar is shorter than the cylindrical body of the actuator  340 , but in other embodiments, it may be the same length or about the same length or longer. 
     As noted, actuator support  479  and actuator  340  are configured to enable the actuator  340  to be removably secured to the actuator support  479 , and thus the actuator positioning mechanism  470 . This removable securement may be, in some embodiments, sufficient to prevent actuator  340  from substantially moving from the retained location in the actuator support  479 , and the actuator positioning mechanism  470  is configured to prevent the actuator support  479  from substantially moving within the artificial passageway  219  during operation of the actuator  340 . For example, the removable securement may be achieved via an interlock between the actuator  340  and the collar that provides retention sufficient to withstand reaction forces resulting from operation of actuator  340 . 
     In an exemplary embodiment, the interlock is provided by an interference fit between inner surface  479 A of the collar of actuator support  479  and an outer surface of actuator  340 . In an alternate embodiment, the interlock is implemented as threads of inner surface  479 A that interface with corresponding threads on the outer surface of actuator  340 . In another embodiment, O-rings or the like may be used to snugly wrap around actuator  340  and snugly fit inside the collar of actuator support  479 . Grooves on the actuator  340  and/or on the collar may be included to receive the O-ring. In other embodiments, compression of the O-ring between the actuator  340  and the collar provides sufficient friction to retain the components in the actuator support  479 . In another embodiment, actuator support  479  or actuator  340  includes a biased extension that is adjusted against the bias to insert the actuator into the support. The extension may engage a detent on the opposing surface to interlock the actuator and the support. Other embodiments include protrusions and corresponding channels on opposing surfaces of the actuator and support. An exemplary embodiment includes a spring-loaded detent that interfaces with a detent receiver of the opposing surface to hold the actuator in the support or that extends behind the actuator once the actuator has been positioned beyond the detent. An alternate embodiment may utilize O-rings to interlock the actuator in the support. Adhesive may be used to interlock the actuator in the support. Any device, system, or method that will interlock the actuator in the support that will permit embodiments detailed herein and/or variations thereof to be practiced may be utilized in some embodiments. 
     The trolley  478 , which is rigidly connected to actuator support  479 , is configured to move linearly in the direction of arrow  3  parallel to the longitudinal direction of extension of arm  477 . In this exemplary embodiment, arm  477  includes tracks with which trolley  478  interfaces to retain trolley  478  to arm  477 . These tracks also establish trolley  478  and arm  477  as a telescopic component configured to enable the adjustment of the location of actuator support  479 , and thus actuator  340  when received therein, relative to the housing  446  (thus the implant body), in at least one degree of freedom (i.e., the degree of freedom represented by arrow  3 ). It is noted that other embodiments may permit adjustment in at least two or at least three degrees of freedom. Thus, when the trolley component is combined with the aforementioned joint  474 , the actuator positioning system enables the location of the actuator  340  to be adjustable relative to the implant body in at least two or at least three degrees of freedom. 
     Movement of the trolley  478  along arm  477  may be accomplished via a jack screw mechanism where the jack screw is turned via a screw driver or a hex-head wrench. Movement of the trolley  478  may also or alternatively be achieved via application of a force thereto that overcomes friction between the trolley  478  and the arm  477 . Any device, system, or method that permits trolley  478  to move relative to arm  477  may be used in some embodiments detailed herein and/or variations thereof. 
       FIG. 5  depicts an alternate embodiment of an external component, external component  442 , which corresponds to an external component usable as the external component  FIGS. 2A-2B  (i.e., in place of the button sound processor  242 ). In this embodiment, there is a behind-the-ear device that includes a behind the ear spine  451  having microphone ports, and ear hook  452 , and a battery  453 . In an exemplary embodiment, the microphone captures sound, and a sound processor in the behind-the-ear device converts that sound into an output signal which is fed to the headpiece  430  (sometimes referred to herein as the communications unit) via cable  420 . That output signal energizes the inductance coil located in the headpiece  430  (which is held against the skin of the recipient via magnet  435 ) to evoke a hearing percept according to the teachings detailed herein. 
       FIG. 6  depicts an alternate embodiment of an exemplary middle ear implant. Here, instead of a receiver unit and stimulator unit combined in a single implantable body (e.g., body  345  of  FIG. 3 ), the receiver unit and the stimulator unit are bifurcated into two separate components coupled together with a connector. More specifically, a receiver unit  644  can be seen, including an inductance coil  610 . A magnet  604  is located inside the perimeter of the inductance coil so as to establish a magnetic attraction with the external component of the prostheses. In this regard, receiver unit  644  corresponds to receiver unit  330  detailed above. Inductance coil  610  is in signal communication with a first connector  610  via electrical lead. This first connector  610  is connected to a second connector  610  that is in turn connected to a so-called intelligent actuator  620  via electrical lead. The intelligent actuator  620  includes an actuator, corresponding to actuator  340  detailed above and a coupling  630  corresponding to coupling  353  detailed above. The intelligent actuator  620  further includes a stimulator unit (or driver unit or drive unit, as it is sometimes referred to). Thus, in this regard, intelligent actuator  620  corresponds to stimulator unit  320  detailed above, plus additional functionalities of the actuator and the coupling. In an exemplary embodiment of use, an external component captures sound utilizing an external microphone, and transduces the sound into electrical signals which are provided to a sound processor located in the external component. The sound processor processes the sound, and outputs a signal to the inductance coil of the external component. The inductance coil of the implantable component receives this signal, and the signal is provided to the intelligent actuator  620 . The intelligent actuator is configured with the stimulator unit to provide signals to an actuator thereof so as to actuate and evoke a hearing percept. In an exemplary embodiment, this stimulator unit is mapped or otherwise contains data associated with the unique features of the recipient or is otherwise calibrated so as to actuate in a specific manner related to the specific recipient for a given signal. Thus, in an exemplary embodiment, the intelligent actuator does not need an additional capsule for power, decoding and/or driving, in at least some exemplary embodiments. 
       FIG. 7  depicts an alternate embodiment utilizing the intelligent actuator of  FIG. 6 . Here, implant body  744  includes a receiver unit, but also includes a sound processor unit  730 . The sound processor unit  730  is in signal communication with an implanted microphone  740 . In this regard, implant body  744  corresponds to a component for a totally implantable hearing prosthesis. As can be seen, signal processor  730  is in signal communication with the intelligent actuator  620  via connectors  610  and the associated leads. Here, sound captured by the implantable microphone  740  is transduced into electrical signals that are provided to the sound processor  730  the sound processor then generate a signal to the intelligent actuator  620 . The signal can be generally the same the signals that are provided by the coil  610  in the embodiment of  FIG. 6 . It is briefly noted that when the implant is being utilized as a totally implantable hearing prosthesis, the coil  610  is only utilized for programming, charging and/or diagnostics, in at least some exemplary embodiments. That said, in some exemplary embodiments, the coil  610  is utilized for sound streaming. In an exemplary embodiment, the same communication protocols utilized for sound streaming as that utilized when the implantable body  744  is receiving signals from the external component based on captured sound by the external component can be used when the implantable body is utilized as part of a partially implantable or semi-implantable hearing prosthesis. That said, in an alternate embodiment, a different protocol for sound streaming can be utilized than that which is utilized for the communication of sound captured by a microphone. 
       FIG. 8  depicts an alternate embodiment of an implant body, including an inductance coil  610 , the sound processor  730 , the implantable microphone  740 , and a stimulator unit  830 . In this regard, the embodiment of  FIG. 8  corresponds to a totally implantable version of the embodiment of  FIG. 3  detailed above. Here, the actuator  340  corresponds to the actuator of  FIG. 3  detailed above. That said, in an alternate embodiment, the intelligent actuator  620  can be utilized. In an exemplary embodiment, the intelligent actuator can be configured to determine whether or not the signals from the implantable body include signals from a stimulator unit, or otherwise simply contain data signals that are to be used by the intelligent actuator zone stimulator unit. Some additional details of this are described in greater detail below. 
       FIG. 9  depicts a variation of the embodiment of  FIG. 7 , where instead of an implantable microphone being part of the implant body  944 , the implantable microphone is part of a remote microphone unit  950  that is in signal communication with the sound processor  730  via connectors  610  and the associated leads. Here, as is the case in the embodiment of  FIG. 7 , the intelligent actuator  620  is in signal communication with the sound processor  730  via the connectors  610  and the associated leads. Note that in an alternate embodiment, the embodiment of  FIG. 9  can correspond to that of  FIG. 8  with respect to the stimulator unit being part of the implant body  944 , and the utilization of the actuator  340 , etc. 
       FIG. 10  depicts a perspective cochlear implant, referred to as cochlear implant  100 , implanted in a recipient, to which some embodiments detailed herein and/or variations thereof are applicable. The cochlear implant  100  is part of a system  10  that can include external components in some embodiments, as will be detailed below. It is noted that the teachings detailed herein are applicable, in at least some embodiments, to partially implantable and/or totally implantable cochlear implants (i.e., with regard to the latter, such as those having an implanted microphone and/or implanted battery). It is further noted that the teachings detailed herein are also applicable to other stimulating devices that utilize an electrical current beyond cochlear implants (e.g., auditory brain stimulators, pacemakers, etc.). It is noted that the teachings detailed herein are also applicable to so-called hybrid devices. In an exemplary embodiment, these hybrid devices apply both electrical stimulation and acoustic stimulation and/or mechanical stimulation to the recipient. Any type of hearing prosthesis to which the teachings detailed herein and/or variations thereof that can have utility can be used in some embodiments of the teachings detailed herein. Further, it is noted that the teachings detailed herein can be applicable to other types of prostheses, such as by way of example only and not by way of limitation, retinal prostheses. 
     In view of the above, it is to be understood that at least some embodiments detailed herein and/or variations thereof are directed towards a body-worn sensory supplement medical device (e.g., the hearing prosthesis of  FIG. 10 , which supplements the hearing sense, even in instances where all natural hearing capabilities have been lost). It is noted that at least some exemplary embodiments of some sensory supplement medical devices are directed towards devices such as conventional hearing aids, which supplement the hearing sense in instances where some natural hearing capabilities have been retained, and visual prostheses (both those that are applicable to recipients having some natural vision capabilities remaining and to recipients having no natural vision capabilities remaining). Accordingly, the teachings detailed herein are applicable to any type of sensory supplement medical device to which the teachings detailed herein are enabled for use therein in a utilitarian manner. In this regard, the phrase sensory supplement medical device refers to any device that functions to provide sensation to a recipient irrespective of whether the applicable natural sense is only partially impaired or completely impaired. 
     As shown, cochlear implant  100  comprises one or more components which are temporarily or permanently implanted in the recipient. Cochlear implant  100  is shown in  FIG. 10  with an external device  142 , that is part of system  10  (along with cochlear implant  100 ), which, as described below, is configured to provide power to the cochlear implant, where the implanted cochlear implant includes a battery that is recharged by the power provided from the external device  142 . 
     In the illustrative arrangement of  FIG. 10 , external device  142  can comprise a power source (not shown) disposed in a Behind-The-Ear (BTE) unit  126 , which can correspond to BTE unit  442  of  FIG. 5 . External device  142  also includes components of a transcutaneous energy transfer link, referred to as an external energy transfer assembly. The transcutaneous energy transfer link is used to transfer power and/or data to cochlear implant  100 . Various types of energy transfer, such as infrared (IR), electromagnetic, capacitive, and inductive transfer, may be used to transfer the power and/or data from external device  142  to cochlear implant  100 . In the illustrative embodiments of  FIG. 1 , the external energy transfer assembly comprises an external coil  130  that forms part of an inductive radio frequency (RF) communication link. External coil  130  is typically a wire antenna coil comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. External device  142  also includes a magnet (not shown) positioned within the turns of wire of external coil  130 . It should be appreciated that the external device shown in  FIG. 10  is merely illustrative, and other external devices may be used with embodiments of the present invention. 
     Cochlear implant  100  comprises an internal energy transfer assembly  132  which can be positioned in a recess of the temporal bone adjacent auricle  110  of the recipient. As detailed below, internal energy transfer assembly  132  is a component of the transcutaneous energy transfer link and receives power and/or data from external device  142 . In the illustrative embodiment, the energy transfer link comprises an inductive RF link, and internal energy transfer assembly  132  comprises a primary internal coil  136 . Internal coil  136  is typically a wire antenna coil comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. 
     Cochlear implant  100  further comprises a main implantable component  120  and an elongate electrode assembly  118 . In some embodiments, internal energy transfer assembly  132  and main implantable component  120  are hermetically sealed within a biocompatible housing. In some embodiments, main implantable component  120  includes an implantable microphone assembly (not shown) and a sound processing unit (not shown) to convert the sound signals received by the implantable microphone in internal energy transfer assembly  132  to data signals. That said, in some alternative embodiments, the implantable microphone assembly can be located in a separate implantable component (e.g., that has its own housing assembly, etc.) that is in signal communication with the main implantable component  120  (e.g., via leads or the like between the separate implantable component and the main implantable component  120 ). In at least some embodiments, the teachings detailed herein and/or variations thereof can be utilized with any type of implantable microphone arrangement. 
     Main implantable component  120  further includes a stimulator unit (also not shown) which generates electrical stimulation signals based on the data signals. The electrical stimulation signals are delivered to the recipient via elongate electrode assembly  118 . 
     Elongate electrode assembly  118  has a proximal end connected to main implantable component  120 , and a distal end implanted in cochlea  140 . Electrode assembly  118  extends from main implantable component  120  to cochlea  140  through mastoid bone  119 . In some embodiments, electrode assembly  118  may be implanted at least in basal region  116 , and sometimes further. For example, electrode assembly  118  may extend towards apical end of cochlea  140 , referred to as cochlea apex  134 . In certain circumstances, electrode assembly  118  may be inserted into cochlea  140  via a cochleostomy  122 . In other circumstances, a cochleostomy may be formed through round window  121 , oval window  112 , the promontory  123 , or through an apical turn  147  of cochlea  140 . 
     Electrode assembly  118  comprises a longitudinally aligned and distally extending array  146  of electrodes  148 , disposed along a length thereof. As noted, a stimulator unit generates stimulation signals which are applied by electrodes  148  to cochlea  140 , thereby stimulating auditory nerve  114 . 
       FIG. 11  depicts an exemplary embodiment of an implantable component of a cochlear implant, where, instead of the receiver stimulator unit being part of an integral component, instead, the receiver unit  644  is bifurcated from the stimulator unit of the cochlear implant. In this regard, element  1020  corresponds to the stimulator unit of the cochlear implant, with element and  30  corresponding to the electrode array. As can be seen, these components are in signal communication with the communication unit  644  via couplings  610  and their respective leads. 
     In an exemplary embodiment, the various components of the implantable prostheses detailed herein can be provided by way of implantable modules that are configured to communicate with one another.  FIG. 12  depicts by way of functional block diagrams a module  1245  which corresponds to the implant body  345  of  FIG. 3 , and a module  1250 , which corresponds to the stimulation arrangement  350 . Herein, contact between the two blocs indicates that the components are in some form of signal communication with each other. By way of example, block  1250  would be in signal communication with block  1245  via cable  328  vis-à-vis  FIG. 3 .  FIG. 13  depicts an alternate example of an embodiment again by way of functional block diagrams, a module  1444  which corresponds to the receiver unit  644  of  FIG. 6 .  FIG. 13  also depicts a module  1320  which corresponds to the intelligent actuator  620  of  FIG. 6 . Again, the contact between the two modules represents signal communication between the communications unit/receiver unit  644  and the intelligent actuator  620  via the connectors  610  and the associated leads.  FIG. 14  depicts an exemplary functional schematic representative of the embodiment of  FIG. 7 , where module  1444  corresponds to the implantable body  744  of that figure, and module  1320  corresponds to the intelligent actuator concomitant with the embodiment of  FIG. 13 .  FIG. 8  depicts an exemplary functional schematic representative of the embodiment of  FIG. 8 , where module  1544  corresponds to the implantable body  844  thereof, and module  1540  corresponds to the actuator  340  and coupling  353  thereof (the stimulation arrangement  350  of  FIG. 3 ). Continuing on,  FIG. 16  depicts an exemplary functional schematic representative of the embodiment of  FIG. 9 , where module  1644  corresponds to the implantable body  944  of  FIG. 9 , module  1650  corresponds to the remote implantable microphone  950  of  FIG. 9 , and module  1320  corresponds to the intelligent actuator  620  of  FIG. 9 . As can be seen, modules  1650  and  1320  are not in contact with each other. This represents that this embodiment requires the module  1644  to “unite” the two, at least with respect to signal communications. Corollary to this is that because module  1650  is shown in contact with module  1644 , and module  1320  is shown in contact with module  1644 , the respective contacting modules are in signal communication with each other.  FIG. 17  depicts an exemplary functional block diagram of a module  1732 , which corresponds to the implantable component of  FIG. 10 .  FIG. 18  depicts an exemplary functional block diagram including module  1344 , which corresponds to the receiver unit  644  of  FIG. 11 , and module  1820 , which corresponds to the stimulator  1020  plus the electrode array  1030  of  FIG. 18 . 
     To be clear, it is noted that in the functional schematics depicting the modules, contact between the two modules as depicted in the FIGS. does not necessarily mean physical contact there between. In this regard,  FIG. 19  depicts an exemplary functional schematic depicting module  1942  contacting module  1732 . Here, module  1942  represents the external component  142  of  FIG. 10 . As noted above, the external component  142  is in signal communication with the implantable component  100  (represented by module  1732 ) via the transcutaneous inductance link. Thus, even though there is a layer of skin and other body tissue between these two modules,  FIG. 19  depicts the modules in contact with each other. Corollary to this is  FIG. 20 , which depicts a module  2042 . Module  2042  represents an external component of a bimodal hearing prosthesis. This external component is in signal communication with the receiver stimulator/implantable component of the cochlear implant  100 , represented by module  1732 . The external component is also in signal communication with a receiver/speaker unit of an acoustic hearing aid that is located in the outer ear or otherwise against the outer ear of a recipient. This receiver speaker unit is represented by module  2060 . Here, module  2042  can represent a behind the ear device, such as behind the ear device  442  of  FIG. 5 . The receiver speaker of the acoustic hearing aid unit can be in signal communication with the BTE device via a cable connection. The BTE device can be in signal communication with the implantable component of the cochlear implant via the transcutaneous inductance field link. 
     While the embodiment of  FIG. 20  depicts the BTE device and the headpiece  430  (corresponding to a communications unit—effectively the same as element  644  detailed above) as being part of a single module, in an alternate embodiment, the two components can be presented in separate modules. According to the teachings detailed herein, this can be done in a scenario where the headpiece  430  of the BTE device could have unique capabilities or otherwise could operate in a different functional manner depending on how that device is utilized. For example, in a scenario where the headpiece  430  is a standard inductance coil that has an input connector, and the inductance coil operates based on the input thereto, the headpiece  430  would not be considered its own module. However, in an exemplary embodiment where the operation of the inductance coil could be changed depending on how it is used (e.g., some coils are deactivated when the inductance coil is utilized to charge the implant as opposed to when the inductance coil is utilized to communicate control information to the implant), the inductance coil could be modularized and considered for the purposes of implementing the teachings detailed herein as a separate module. To this end,  FIG. 21  depicts an exemplary embodiment of the spine for 51 of the BTE device  442  of  FIG. 5 , represented by module  2140 , in signal communication with module  2130 , which corresponds to the communication unit  430  of  FIG. 5  (the inductance coil), which in turn is in communication with module  1732 , which represents the implantable component of the hearing prosthesis of  FIG. 10 . This is as contrasted with the embodiment of  FIG. 20 , where the inductance coil/communications unit (headpiece) of the BTE device is part of the module that includes the spine  451  of the BTE. 
     It is noted that while the above modularization and the teachings detailed herein are directed towards various components of a hearing prosthesis detailed herein, the modularization according to the teachings detailed herein are also applicable to other types of hearing prostheses/other components thereof. Further, the teachings detailed herein are applicable to other types of prostheses, such as by way of example, retinal implants or other sense implants. In this regard, the teachings detailed herein are but exemplary, and are applicable beyond the specific teachings detailed herein. 
     In an exemplary embodiment, one or more or all of the modules of a given module system (hereinafter, the aggregate of modules in signal communication with other modules is referred to as a module system) contain a set of utilitarian information regarding its own status and relationship to the overall system. The modules can include a chip, such as by way of example only and not by way of limitation, a nonvolatile memory chip, which contains information or otherwise stores information or otherwise stores data therein/thereon in a manner that permits the data to be stored over long periods without energy input (e.g., months, years, etc.). In some exemplary embodiments, such data can include by way of example only and not by way of limitation, module manufacturing information, model and serial number; parameters specific to the module, e.g. microphone sensitivity, actuator transformer constant; parameters specific to the recipient, e.g. implantation date, audiologic fitting parameters (gain by frequency, compression ratio and knee point), type of surgery and location of actuator (incus body, stapes capitulum, round window, etc.); and parameters specific to the implanted system, e.g., bilateral versus unilateral, microphone location, type of actuator, etc. In an exemplary embodiment, the modules are configured to transmit the data to another module and/or otherwise enable another module to read the data there from. Note further that in an exemplary embodiment, the modules are configured to read the data from another module, at least providing that the other module enables such reading. 
     In view of the above, it is to be understood that the modules can be configured so as to have the capability of communicating amongst themselves. In an exemplary embodiment, the modules or otherwise the module system is configured to prompt or otherwise enable the communication amongst themselves without instructions or otherwise prompting from outside the system. As will be detailed below, in an exemplary embodiment, the modules are configured so as to be self-reconfiguring and/or so as to enable one or more modules to reconfigure one or more other modules or at least instruct one or more other modules to reconfigure themselves. By way of example only and not by way of limitation, with respect to the module  2130  of  FIG. 21 , module  2130  can receive input from module  2140  corresponding to output from a signal processor/sound processor, and thus generate an inductance field based on that input. In another exemplary embodiment, the module  2130  can receive input from a power source or the like, and, based on that input, reconfigure itself so as to utilize fewer of the inductance coils so as to be more efficient when generating the inductance field to recharge the implantable component. Alternatively and/or in addition to this, the module  2130  can be configured so as to determine that instead of BTE spine  2140  in signal communication therewith, a charger component or the like utilized to specifically charge the implantable component, is in signal communication with the module  2130 . Based on the recognition that this other type of component is now in signal communication with the module  2130 , the module  2130  can reconfigure itself for recharging the implantable component. Subsequent to this, if module  2140  is again placed into signal communication with module  2130 , and/or the recharging model is taken out of signal communication with module  2130 , module  2130  can reconfigure itself back to the configuration that is optimized or otherwise more efficient for transmission of control signals to the implant to evoke a hearing percept. Note also that in alternate embodiments, module  2140  or the recharging module can be configured to instruct the module  2130  to reconfigure itself accordingly. 
     The communications between the modules may be executed by way of example only and not by way of limitation, and thus the modules may be configured to communicate via wired connection from the transmitting to the receiving module; wired connection from the transmitting, through an intermediate module, to the receiving module; wireless connection by implanted coil or antenna from the transmitting to the receiving module using near-field (inductive) or medium-field coupling; wireless connection in both directions between the implanted module and an external device such as an audiologist&#39;s programming interface or the recipient&#39;s own sound processor and/or wireless connection between one and any number of other modules using the external device as an intermediary. Any device, system, and/or method of communication between the modules can be utilized in at least some exemplary embodiments. In an exemplary embodiment, the modules can include, by way of example only and not by way of limitation, an implantable coil with connector, an intelligent actuator with RF decoder and driver, capable of receiving both power and audio signal from a coil, and also two-way communication with an external device or another module, an implantable sound processor with battery and integrated microphone, an implantable sound processor with battery and pendant microphone and/or an implantable intelligent microphone. To this again, in an exemplary embodiment, a given system can include a plurality of modules that are in turn in communication with a plurality of modules or otherwise are enabled to be placed or otherwise placed themselves into signal communication with a plurality of modules. By way of example only and not by way of limitation, with respect to the embodiment of  FIG. 16 , the implantable remote microphone represented by module  1650  could be configured to also communicate with the intelligent actuator represented by module  1320 , at least in an exemplary embodiment where the intelligent actuator further includes a sound processor that can be redundant to the sound processor of module  1644 . This is depicted by way of example in  FIG. 22 , where module  1650  is depicted as contacting module  1644  and module  1320 , and module  1320  is depicted as contacting module  1644  and module  1650 . 
     At least some exemplary embodiments of the teachings detailed herein can have utilitarian value with respect to enabling the combination and/or recombination and/or the decombination, etc. of modules of a module system as circumstances associated with the recipient change or otherwise other changes occur, where such changes can have utilitarian value. The following will be described in terms of some exemplary scenarios of changing a given system by removing and/or incorporating additional modules. The following exemplary scenario is just that, exemplary. It is to be understood that other exemplary scenarios are applicable to the teachings detailed herein and/or variations thereof. 
     By way of example only and not by way of limitation, an initial scenario may exist where a module system that includes an implantable component is implanted in a pediatric recipient. Initially, the pediatric recipient is implanted with only the communication unit  644  (e.g., the receiver coil) and an implantable intelligent actuator  620 . This corresponds to the embodiment of  FIG. 6  and  FIG. 13  detailed above. The implantable portion of the system is represented in modular form by  FIG. 13 , where module  2342  corresponds to the external component  242  of  FIG. 2A , which external component includes an inductance coil configured to communicate with the communications module  1344 . In this regard, the system of  FIG. 23  is utilized exclusively with an external sound processor located in module  2342 . 
     In this exemplary scenario, module  1320  is initially programmed or otherwise configured with data/information residing in nonvolatile memory thereof. In an exemplary embodiment, a portion of the nonvolatile memory (e.g., a block thereof), includes information/data enabling identification of that module when read or otherwise accessed. By way of example only and not by way of limitation, the information/data can include the actuator module, the serial number of the module and/or of the actuator, the manufacturing date, etc. Indeed in an exemplary embodiment, case specific/recipient specific information can be included or otherwise stored in the memory. By way of example only and not by way of limitation, a recipient identification information can be stored in the memory, the implant center information to and/or the implant date can be stored in the memory. Still further, in another block of the nonvolatile memory, parameters specific to the recipient&#39;s method of ossicular attachment can be stored therein. By way of example only and not by way of limitation, information relating to attachment to the incus body, the incus long process, the stapedotomy or round window membrane can be stored therein. Still further, in an exemplary embodiment, the nonvolatile memory includes information or data relating to mapping of predicted output in equivalent SLP to input voltage. Any data or information having utilitarian value can be stored in the memory. 
     In an exemplary embodiment, the system of  FIG. 23  is configured such that the external component  2342  can access this data or otherwise access at least some of the data. In an exemplary scenario, the external module  2342 , which includes the sound processor, is configured to access this data and configure or otherwise adjust a processing regime of the sound processor based on this data so as to deliver a voltage based on the recipients fitting parameters and then translate such to the desired auditory stimulation level. In an exemplary embodiment, the external module  2342  is configured to read the data from the memory in module  2320 . In an exemplary embodiment, the external module  1324  is configured to automatically read the data from the memory in module  2342  upon being placed into signal communication with module  1344  which is in signal communication with module  1320 . Alternatively, and/or in addition to this, the module  1320  is configured to upload or otherwise output the data to the external component/module  2342  via module  1344  upon module  2342  being placed into signal communication with module  1344 . 
     It is briefly noted that for purposes of linguistic economy, any disclosure of a first module reading data from a memory of a second module corresponds to a disclosure of the alternate embodiment and/or the additional embodiment of the second module uploading that data to the first module, unless otherwise noted. 
     The following is directed towards operation of the system of  FIG. 23  when the intelligent actuator  1320  is being utilized in the intelligent mode. That is, the intelligent actuator  1320  is configured to operate based on a received input directly based on an RF signal or the like, and deconstruct that signal into a “stimulation signal” to be outputted to the actuator of the intelligent actuator. Basically, the intelligent actuator serves in part as the stimulator of the embodiment of  FIG. 3  detailed above. In an exemplary embodiment, module  1320  (the intelligent actuator) contains a logic circuit that is configured to detect the signature of the external module  2342  and/or a signature of another module (more on this below). In an exemplary embodiment, the module  1320  is configured such that, when the external module  2342  is detected, module  1320  passes those signals received from module  1344  to an RF decoder circuit contained within module  1320  or otherwise in signal communication with module  1320  so as to decode the input signal with respect to a utilitarian coding regime (e.g. PWM or Sigma Delta, etc.). The ability to decode the input signal can have utilitarian value with respect to scenarios where the input to the module  1320  corresponds to the RF signal from module  1344 , such as when the system is in the configuration of  FIG. 23 . This is because the “stimulator” component of the intelligent actuator is driven by the RF signals from the external module  2342  which have been transmitted to the internal communication module  2344 . Alternatively, and/or in addition to this, the external component numeral  2342  can embed a code into the signal transmitted to the implantable module  1344 , and the implantable module  1320  can be configured to read or otherwise detect that signal, and recognize that the signal should be provided to the RF decoder circuit. Thus, the module  1320  need not necessarily recognize that the external module  2342  is in signal communication there with. Any device, system, and/or method that can enable the system of  FIG. 23  to recognize that a given signal requires RF decoding and thus the decoding functionality of module  1320  or another module of the system should be engaged can be utilized in at least some exemplary embodiments. 
     Continuing with the exemplary scenario of use, as the recipient matures from the pediatric state, or otherwise as technology advances, there becomes a point in time where it is utilitarian to upgrade the system to a so-called totally implantable system. In this regard,  FIGS. 7 and 8  detailed above depict totally implantable middle ear implant systems, the difference between the two being that the embodiments of  FIG. 8  utilizes the standard actuator of the embodiment of  FIG. 3 , and the embodiment of  FIG. 7  utilizes the intelligent actuator  620 . In an exemplary embodiment, the entire prosthesis is explanted (e.g., modules  1344  and  1320  are removed from the recipient), albeit the coupling component to the ear system may be left in place for later use, and the prosthesis of  FIG. 8  is implanted in its place. However, it can also be utilitarian to instead maintain the actuator as implanted/in its implanted location. This thus corresponds to maintaining the intelligent actuator  620  implanted in the recipient. Accordingly, in an exemplary embodiment, the connection between the intelligent actuator  620  and the receiver unit  644  can be broken at connectors  610 , and the implantable body  744  of  FIG. 7  can be instead connected thereto (implantable body also being implanted in the recipient). The resulting implanted portion of the system can be seen in  FIG. 25 , which corresponds to the arrangement of  FIG. 14 , with the nomenclature that module  1320  is the old module  1320  ( 1320  OLD). 
     In an exemplary embodiment, the old module  1320  (module  1320  OLD—hereinafter, the nomenclature “OLD” will be dispensed with) is configured to accommodate the fact that it no longer receives “raw” RF signals from communication module  1344 . Instead, it receives signals that are analogous to indoor the same as the signals that it is internal stimulator (the stimulator of the intelligent actuator) outputs to the actuator. That is, the functionality of the module  1320 /the intelligence actuator has been reduced to that of actuator  340  of  FIG. 3 . In this regard, module  1320  can include a logic circuit, which can be the same logic circuit detailed above or another logic circuit, which detects the signature of the module  1444  in general, and that of the implantable sound processor  730  in particular. Module  1320  is configured such that if the signature is present, the input from module  1444  (the input from the implantable sound processor  730 ) is directed through an output mapping circuit of the module  1320 /intelligent actuator, to the actuator. This is as contrasted to the scenario of use detailed above, where the old module  1320 /intelligent actuator decoded the RF signals received from module  1344 . That is, because the intelligent actuator is no longer receiving raw RF signals, but instead receiving the refined output of the implantable sound processor  730 /the equivalent of output from stimulator unit  320 /the stimulator unit of the intelligent actuator, the intelligent actuator need not decode those signals. 
     Concomitant with the embodiment of  FIG. 23 , the module  1444  can be configured to embed a code into the output thereof to the intelligent actuator/module  1320 . The intelligent actuator/module  1320  can be configured to read that code, and recognize that the intelligent actuator need not decode the signal. That said, in an alternate embodiment, module  1320  can be configured to automatically analyze a given signal, and determine that the signal is or is not an RF signal, and operate accordingly. Also, consistent with the embodiment of  FIG. 23 , module  1444  can be configured to output a signal to module  1320  instructing module  13202  operate accordingly. Note also that in an exemplary embodiment, consistent with the embodiment of  FIG. 23 , module  1444  can be configured to output and identification signal to module  1320 , and module  1320  can be configured to read that identification signal, and recognize that it is in signal communication with module  1444 , and operate accordingly. (Module  2342  can also be configured to output such an identification signal.) Note also that in an exemplary embodiment, module  1320  can be configured to read a memory in module  1444  and/or module  2342  and determine how module  320  should operate accordingly. Any device, system, and/or method that will enable module  1320  to recognize how it should operate based on the fact that it is in communication with another module can be utilized in at least some exemplary embodiments. Corollary to this is that any device, system, and/or method that will enable module  1320  to recognize how it should operate based solely and entirely and only on the fact that it is in communication with another module can be utilized in at least some exemplary embodiments. With regard to these features, at least some of the embodiments detailed herein can have utilitarian value with respect to enabling a given automatic reconfiguration and/or automatic change of operation and/or automatic change of functionality of a first module upon a second module being placed into signal communication with that first module. This as opposed to having a user, such as a healthcare professional, such as a surgeon, reconfigure or otherwise instruct the various modules (e.g., by activating a switch, by programming, etc.) to operate differently. 
       FIG. 26  presents some exemplary logic flow assigning functionality to the given modules according to an exemplary embodiment of the embodiment of  FIG. 25  after the embodiment of  FIG. 23  is updated to the totally implantable system. It is briefly noted that module  1444  of  FIG. 24  is presented with additional details relating to a scenario where module  1444  is instead module  1644 , and the remote pendulum microphone  950  is in signal communication therewith. Indeed, in an exemplary embodiment, module  1444  can also be in signal communication with a pendulum microphone  950 , as will be detailed below. 
     Note that  FIG. 26  depicts additional details relating to a remote programmer, which details will be provided below. 
     With regard to  FIG. 26 , it can be seen that the module  1444 , can include such data stored therein, such as in a memory of the like, data relating to the model of the module and/or sound processor, the serial number thereof, the manufacturing date, the recipient ID, the center that such was made and/or the center at where such was implanted, and the implantation date. Module  144  can further include data stored in a memory relating to recipient parameters, such as by way of example only and not by way of limitation, thresholds, UCLs, compression/expansion data, such as ratios and/or kneepoints. In an exemplary embodiment, module  1444  can further include such data as the battery state, the usage history, etc. As will be detailed below, module  1444  can also include a logic circuit to determine if it is being operated in a hybrid mode, and thus can be configured to output signals to a cochlear implant. With respect to the scenario where module  1644  is instead being utilized, any of the aforementioned data associated with module  1444 , but directed to module  1644 , can be stored therein in the memory of module  1644 . Note also that data relating to microphone parameters, such as by way of example only and not by way of limitation, sensitivity data obtained from the fitting process, etc. can be stored in that module  1644 . As will be detailed below, module  1444  and/or module  1644  includes a logic circuit that evaluates whether or not the battery is flat or will become flat (a “disablement mode”), as is schematically represented by the flowchart depicted in  FIG. 26 . d    
     It is noted that in the exemplary embodiment of  FIGS. 7 and 14 , where the implantable sound processor  730  is integrated with an implantable microphone  740  (e.g., implantable body  744 /module  1444  includes both the sound processor  730  and the microphone  740 ), implantable body  744 /module  1444  can include memory, such as nonvolatile memory, in which programming or data or the like is stored at the time of implantation into the recipient. In an exemplary embodiment, the memory can include identifying information that can be available for retrieval at a subsequent temporal period (e.g., serial number, manufacturing date, information about the recipient, such as the recipient ID, the implant center, the implanted dates, the model of the sound processor, the model of the microphone, etc.). Also, the memory can include (as part of, for example, the same block of the nonvolatile memory, or a different block of the nonvolatile memory) fitting parameters specific to the recipient, such as by way of example only and not by way of limitation, thresholds, compression and/or expansion ratios, kneepoints, UCLs, etc.). Any data having utilitarian value with respect to the teachings detailed herein and/or with respect to operating a hearing prosthesis can be utilized or otherwise stored in the memory of the implantable body  744 /module  1444 . 
     In an exemplary embodiment of use/implantation, as noted above, module  1320  is the old module. When module  1320  is connected via the connectors  610  to module  1444 , in an exemplary embodiment, module  1320  detects the signature of the module  1444  (e.g., the signal processor  730  and output a signature and/or can have a signature they can be read by module  1320 , etc.). In an exemplary embodiment, this occurs automatically upon (which includes subsequent) to the establishment of signal communication between module  1444  and module  1320 . Upon such occurrence, module  1320  automatically reconfigures itself so as to direct the input from module  1444  to the output mapping circuit and the actuator motor of module  1320 . This as opposed to directing the output from module  1444  to the RF decoder circuitry of module  1320 . That is, module  1320  automatically reconfigures itself so as to operate in the non-intelligent mode/to operate in a manner akin to the traditional actuator  340  of  FIG. 3 . That said, alternatively and/or in addition to this, module  1444  is configured to look for module  1320  (or any other module) upon a new module being placed into signal communication there with (analogous to a Windows computer looking for a flash drive). Module  1444  is configured to identify module  1320  when placed into signal communication therewith, and instruct module  1320  to operate in the non-smart mode, or otherwise reconfigure module  1320  such that it will operate in the non-smart mode. Again, unless otherwise specifically detailed herein, in at least some exemplary embodiments, all modules are configured to both instruct or otherwise control another module and be controlled and be instructed by another module. Also, unless otherwise specifically detailed herein, all modules are configured to output data from the memory, and enable the data from the memory to be read. Any permutation of this can enable the reconfigurations of a given module. 
     In an exemplary embodiment, the above identification/control/reconfigurations, etc. occurs automatically, and is transparent to the surgeon and/or clinician who is implanting the module  1444 . In this regard, in an exemplary embodiment, an exemplary method of surgery entails, after obtaining access to the implant system including modules  1344  and  1320 , disconnect module  1344  from module  1320 , remove module  1344  from the recipient, connect module  1444  to old module  1320 , secure module  1444  to tissue of the recipient. In an exemplary embodiment, these are the only method actions executed between the time just before the module  1344  is disconnected from module  1320  to just after the time that module  1444  is secured to tissue of the recipient and/or just after the time that module  1444  is connected to old module  1320  so as to have a fully functioning totally implantable hearing prosthesis in the recipient. In this regard, in an exemplary embodiment, a surgeon or other healthcare professional or the like need not make adjustments for provide input into the module  1320  and/or the module  1444  to make the two modules work with each other so as to establish a hearing percept. That said, in an exemplary embodiment, fitting data or the like from module  2342  could be transferred to module  1444  prior to implantation or after implantation. However, that data simply customizes module  1444  to the recipient. That is, the data makes module  1444  and module  1320  more functional—those modules are already functional and the first instance. 
     It is noted that the embodiment of  FIGS. 7 and 14  and the embodiments of  FIGS. 8 and 15 and 9 and 16  are configured so as to function or otherwise continue to enable the evocation of a hearing percept in the event of a failure or otherwise inability of the implanted sound processor  730 . By way of example only and not by way of limitation, in an exemplary embodiment, the implantable battery located in the implantable body  744 ,  844 , and  944  could become discharged, thus preventing the sound processor  730  from being powered. Still further, in an exemplary embodiment, the implantable microphone  740  could fail, and thus, because input to the sound processor based on captured sounds is not available, the sound processor  730  does not have input to process, and thus cannot output useful signals to the actuator  1320 . In any event, whatever the “failure mode” or “disable mode,” some exemplary embodiments of the totally implantable hearing prostheses are configured to operate in partially implantable mode. For example,  FIG. 27  depicts the modules  1444  and  1320  OLD in signal communication with external component/module  2342  of the embodiment of  FIG. 3 . 
       FIG. 24A  depicts an exemplary logic flow assigning functionality for the various modules of  FIG. 27 , along with some additional details about an external programming system that will be briefly described in greater detail below. It is briefly noted that as with  FIG. 26 , module  1444  of  FIG. 24  is presented with additional details relating to a scenario where module  1444  is instead module  1644 , and the remote pendulum microphone  950  is in signal communication therewith. Indeed, in an exemplary embodiment, module  1444  can also be in signal communication with a pendulum microphone  950 , as will be detailed below. 
     With regard to  FIG. 24A , it can be seen that the module  1444 , can include such data stored therein, such as in a memory of the like, data relating to the model of the module and/or sound processor, the serial number thereof, the manufacturing date, the recipient ID, the center that such was made and/or the center at where such was implanted, and the implantation date. Module  144  can further include data stored in a memory relating to recipient parameters, such as by way of example only and not by way of limitation, thresholds, UCLs, compression/expansion data, such as ratios and/or kneepoints. 
     The implanted module  1444  can also include any of the data just detailed with respect to module  2342 , but directed to the module  1444 . In an exemplary embodiment, module  1444  can further include such data as the battery state, the usage history, etc. Note also that this data can also be present in the module  2342 , but directed to module  1444 . As will be detailed below, module  1444  can also include a logic circuit to determine if it is being operated in a hybrid mode, and thus can be configured to output signals to a cochlear implant. With respect to the scenario where module  1644  is instead being utilized, any of the aforementioned data associated with module  1444 , but directed to module  1644 , can be stored therein in the memory of module  1644 . Note also that data relating to microphone parameters, such as by way of example only and not by way of limitation, sensitivity data obtained from the fitting process, etc. can be stored in that module  1644 . Again, as will be detailed below, module  1444  and/or module  1644  includes a logic circuit that evaluates whether or not the battery is flat or will become flat (a “disablement mode”), as is schematically represented by the flowchart depicted in  FIG. 24A . 
       FIG. 24B  presents a schematic representing logic associated with a system that further includes an implantable intelligent microphone (here, two microphones) represented by modules  1650 . The utilitarian features of this implantable microphone will be described in greater detail below. However, as can be seen, the implantable intelligent microphone embodied by module  1650  can be placed into signal communication with module  1444  and/or module  1644 . The module  1650  can include data related to that implantable microphone along the lines of that related to module  1444  and/or the module  2342 . In an exemplary embodiment, information or otherwise data relating to the specific microphone parameters can be stored therein, such as by way of example only and not by way of limitation, the sensitivity data resulting from the fitting operation. Note also that data indicative of the implantation sides of the modules  1650  can also be stored in a memory thereof, such as whether or not the microphone is implanted on the left side or the right side of the recipient, or which side the microphone is implanted, etc. It is noted that the features associated with modules  1650  seen in  FIG. 24B  are also applicable to the system of  FIG. 26  and the other functional logic block diagrams detailed herein and variations thereof. 
     Here, the module  2342  captures sound and processes that captured sound just as it would have done in the embodiment of  23  prior to conversion of the implant to the fully implantable system. The process sound is converted into a RF signal and transmitted from module  2342  to module  1444 , where coil  610  receives that signal. In this exemplary embodiment, module  1444  is configured to automatically recognize that it is incapable of processing signals from the microphone for whatever reason, and thus is configured to automatically place itself into a pass-through mode so as to pass the signal received by coil  610  to the actuator  620  (module  1320  OLD). By way of example only and not by way of limitation, a logic circuit within module  1444  can be configured to detect a low battery level or the like, and thus redirect input (or control the components of module  14442  redirect input) from the coil  610  directly to the actuator  620  (module  1320  OLD). In an exemplary embodiment, module  1444  is configured to automatically instruct module  1320  OLD to treat the signals from module  1444  as RF signals. In an exemplary embodiment, upon the occurrence of the failure mode and/or the disablement mode, module  1444  is configured to automatically provide an indication to module  1320  that it is instead module  1344  (communications unit/receiver unit  644 ) or otherwise treat signal there from as if those signals were from module  1344 . In an exemplary embodiment, module  1444  can be configured to embed a code into the output thereof that will be read by module  1320  OLD such that module  1320  OLD will treat the signal as an RF signal and operate accordingly. Alternatively, and/or in addition to this, in an exemplary embodiment, module  1320  OLD is configured to detect that there exists a code and/or there is an absence of a code in the signal from module  1444 , and thus reconfigure itself to operate in the intelligent actuator mode. In an exemplary embodiment, module  1320  OLD is configured to read or otherwise evaluate the status of module  1444 , and upon a determination that module  1444  has experienced a failure mode and/or a disablement mode, operate in the intelligent actuator mode. 
     To be clear, in an exemplary embodiment, there is a method where an implanted battery goes flat or otherwise goes to a low-power state, and the system self-reconfigures into a semi-implantable hearing prosthesis, passing the signal from the external sound processor through to the actuator or to the other intelligent components thereof so as to evoke a hearing percept. In an exemplary embodiment, this action is automatic upon the battery going flat, in an alternate embodiment, this action is automatic when the battery power capacity reaches a low level or otherwise when a low level battery capacity is detected. That said, alternatively, and/or in addition to this, the reconfiguration of the system to a partially or semi implantable hearing prostheses can be executed via a “manual” invocation thereof. 
     In view of the above, it can be understood that in an exemplary embodiment, there is an implantable device, such as by way of example only and not by way of limitation, an implantable hearing prosthesis, comprising an implantable module (e.g., module  1444 ), including a first functional component (e.g., sound processor  730 ). In this exemplary embodiment, the implantable module is configured to effectively differentiate between a plurality of different second functional modules respectively placeable into signal communication with the module. In an exemplary embodiment, the different second functional modules can be selected from the group of the intelligent actuator module  1320 , the standard actuator module  1540 , the pendulum microphone module  1650  (intelligent or standard microphone), the cochlear implant stimulator module  1020  (intelligent or standard stimulator), etc. Consistent with the teachings detailed above, the implantable module of this exemplary embodiment is configured to analyze respective signals from the plurality of different second modules and determine a respective functionality of the second modules based on the respective signals. In an exemplary embodiment, this corresponds to a scenario where one or more of the second modules outputs an identification signal to the implantable module indicating its functionality or otherwise what module it is (intelligent actuator, pendulum microphone, bone conduction actuator, implantable battery module, etc.). In an exemplary embodiment, this corresponds to a scenario where the implantable module analyzes standard operational signals from these modules with respect to a closed circuit extending between the implantable module and the respective second modules to determine the respective functionality of the second modules. By way of example only and not by way of limitation, with respect to the embodiment where module  1020  is placed into signal communication with module  1444  or another implantable module, module  1444  or another implantable module could analyze the impedance of the given circuit to determine that module  1020  is placed into signal communication therewith. This can also be the case with respect to any of the other modules. For example, with respect to the modules corresponding to the remote pendulum microphones, the implantable module could analyze the signal and recognize, based on the frequency content thereof, that such corresponds to an audio signal, and because the implantable module has logic or otherwise is programmed to recognize that such a signal corresponds to a remote pendulum microphone, determine that the second module is a microphone module. Still further by way of example only and not by way of limitation, with respect to a remote inductance coil module, the implantable module could be configured to analyze the signal and determine that such signal corresponds to an RF signal, and because the implantable module is programmed or otherwise contains logic to identify such a signal as an RF signal, can determine that the module is a inductance coil module. It is noted that in some exemplary embodiments, lookup tables or the like can be utilized. Any device, system, and/or method that can enable the implantable module to analyze respective signals from the different second modules and determine the respective functionality thereof based on the signals can be utilized in at least some exemplary embodiments. 
     By “effectively differentiate,” it is meant that the implantable module can affirmatively differentiate between different modules placed into signal communication there with (e.g., the module knows that another module is a module for X, Y or Z etc.), and also that the implantable module can affirmatively differentiate between different modules because one module is acting differently than another module and/or that a given module is not providing data or otherwise is not reacting as it would if it was one such module. By way of example only and not by way of limitation, the implantable module could default to a conclusion that any module in signal communication there with that does not have identifying information is a microphone module or an inductance coil module (i.e., a module that does not have an active component). Thus, it would effectively differentiate between modules even though it is not affirmatively identifying the module. 
     Still further, in an exemplary embodiment, it can be understood that the implantable module is configured to adjust an operational parameter of the functional component based on the effective differentiation. In an exemplary embodiment, such as where the module is the intelligent actuator module  1320 , the functional component can be a tissue stimulation device, and the implantable module is configured to enable the tissue stimulation device to operate differently based on the effective differentiation. With reference to the above exemplary scenario, if the intelligent actuator module  1320  determines that it is in signal communication with an inductance coil module corresponding to  1344 , the module  1320  will control the tissue stimulation device to operate in the intelligent actuator mode, decode the RF frequencies and develop stimulation/driver output based on those received RF frequencies, which output is provided to the actuator of module  1320  to evoke a hearing percept. Conversely, if the intelligent actuator module  1320  determines that it is in signal communication with an implantable sound processor or the like (even if such determination is simply based on the fact that the signal is not an RF signal, thus effectively differentiating between a signal from an implantable signal processor module and from an implantable inductance coil module), the module  1320  will pass the signal directly to the actuator without the decoding and without generating a stimulator/driver signal. That is, the module  1320  will place the tissue stimulation device into the standard mode of operation. Corollary to this is that in an exemplary embodiment, the implantable module is configured to enable the tissue stimulation device to selectively operate under one of two regimes based on the effective differentiation. In an exemplary embodiment, the first regime of the two regimes is an operation of the tissue stimulating device in a smart device mode (e.g., that which decodes the RF signal and develops a stimulation/driver signal based thereon—the intelligent actuator mode). In an exemplary embodiment, the second regime of the two regimes is an operation of the tissue stimulating device in a slave mode (e.g., module  1320  receives the stimulation/driver signals from module  1444  and operates the actuator based solely on those signals—the standard mode of the intelligent actuator). 
     By “smart mode,” it is meant a mold in which the module operates in a more autonomous manner than that of the “slave mode.” By “slave mode,” it is meant that the module operates as a slave to the other module. That is, it is controlled by the other module. This is differentiated from operation where the module receives a signal and analyzes the signal and develops an operation mode based on the analysis. Again, with respect to the exemplary embodiment of the smart actuator, the slave mode is that which the intelligent actuator receives stimulation/driver signals and applies those driver signals to the actuator. In an exemplary embodiment of slave mode with respect to an intelligent cochlear implant electrode array (described in greater detail below) would be the receipt by module  1820  of a stimulation signal/drive signal from an implantable sound processor module, where the module  1820  stimulates tissue utilizing the electrode thereof bypassing that stimulation signal/drive signal directly to the electrodes. 
     Note also that in view of the above, it can be understood that in an exemplary embodiment, there is an implantable system, such as by way of example only and not by way of limitation, the system of  FIG. 6 , wherein there exists a first implantable module having a first role in the implantable system. By way of example only and not by way of limitation, that can be the module  1320  detailed above, with a role of that of a stimulator/driver combined with actuation functionality. In this exemplary embodiment, this implantable module, such as module  1320 , is configured to adopt a second role automatically upon a changed circumstance. In an exemplary embodiment, the second role would be that of a standard actuator where the stimulator/driver functionality has been disabled. Such a changed circumstance can correspond to an upgrade of the prosthesis of which module  1320  is apart from a partially implanted prosthesis to a fully implantable prosthesis. Still further, in an exemplary embodiment, an exemplary implantable system can correspond to that of  FIG. 7 , where the first implantable module having a first role in the implantable system corresponds to module  1444 , where again, module  1444  is configured to adopt a second role automatically upon exchange circumstance. In an exemplary embodiment, the first role would be that of a receiver plus an implantable speech processor, while the second role would be that of a receiver, where the module  1444  would simply pass the RF signals received by coil  610  to the module  1320 , such as in the scenario where there is a failure mode or a disablement mode or a degraded mode, etc. 
     In view of the teachings herein, it is to be understood that in an exemplary embodiment, the first implantable module can include a signature detection functionality to analyze the signal from a module remote from the first module. This implantable first module can be configured such that, based on the analysis of the signal, the first implantable module determines that a circumstance has changed and adopt the second role. Consistent with the teachings detailed herein, in an exemplary embodiment, the first module can be module  1320 , where the module  1320  is configured to analyze a signature of the module  1444 , and, based on that analyzed signature, determine that it should operate in standard mode as opposed to intelligent actuator mode because there is a signal processor implanted in the recipient signal communication there with. 
     Still further, it is to be understood that in an exemplary embodiment, there exists an implantable system that includes the aforementioned first module along with a second module, where the second module has a functionality of a tissue stimulator. Again, this can be module  1320  although in other embodiments, this could be other modules as detailed herein. The first role of the first module (e.g.,  1444 ) is that of a sound processor that receives a sound signal from an implantable microphone and wired communication with the sound processor. That first role further includes the ability to output a first control signal to a tissue stimulator in signal communication with the first module to activate the second module (e.g., module  1320 ) to stimulate tissue based on the first control signal. In an exemplary embodiment, the second role of the first module (e.g.,  1444 ) is that of at least one of: (i) a receiver-stimulator that receives a signal from an external module external to the recipient and provides a stimulator control signal based on the received signal to activate the second module to stimulate tissue; or (ii) a pass-through device that receives the signal from the external module external to the recipient and provides the signal to the second module to activate the second module to stimulate tissue based on the received signal. 
     Corollary to the teachings above, in an exemplary embodiment, the system includes a second module in signal communication with the first module. The first implantable module is configured to send a first signal to the second module indicating the functionality of the first module. The second module is configured to automatically adapt itself to function differently upon receipt of the first signal so that the second module is operationally compatible with the first module. In an exemplary embodiment, the first module can be module  1444 , and the second module can be module  1320 , where module  1320  adapts itself to function as a standard actuator as opposed to an intelligent actuator upon receipt of this first signal. That said, that first signal can be a signal from the module  1444  indicating that the actuator  1320  should operate in the intelligent actuator mode, because there exists a disablement mode and/or a failure mode of module  1444 . Still further, the first module can be an external component of the hearing prostheses, as will now be described. 
     While the embodiments detailed above have been directed towards the scenario where module  1444  experiences some type of failure mode and/or disablement mode, in an alternate embodiment, there need not be some form of failure mode and/or disablement mode to result in the configuration of  FIG. 27 . By way of example only and not by way of limitation, a recipient may find that the sound quality of a hearing percept based on the implanted microphone is not as utilitarian as that which might be the case from a microphone located external to the recipient. In this regard, the recipient may place the module  2342  against his or her head, and thus establish signal communication between module  2342  and module  1444 . In an exemplary embodiment, module  1444  can be configured to identify the presence and/or absence of module  2342 , and thus reconfigure itself to operate in the aforementioned pass-through mode instead of the sound processing mode. In an exemplary embodiment, codes can be provided from a signal from module  2342  instructing module  1444  to operate in the pass-through mode. In an exemplary embodiment, module  2342  can simply instruct module  1444  to operate in the pass-through mode. 
     Corollary to all of the above is that in an exemplary embodiment, there is an implantable module that can differentiate between modules as detailed above, where the implantable module is configured to differentiate between an implantable signal processor and an external signal processor based on a received signal (whether that signal is automatically generated from the implantable signal processor module with the external signal processor module, or whether that signal is a result of an interrogation by the implantable module of the external signal processor module or the implantable signal processor module). 
     Note also that in some alternate embodiments, module  1444  can be configured to provide signals based on sound captured by both the external module  2342  and the implantable module  1444 . The intelligent actuator  620  (module  1320  OLD) can be configured to receive both signals perhaps in an interleave manner or the like, or via separate leads, and evaluate the signals and determine which signal should be utilized to evoke a hearing percept. Indeed, the signals can arrive from two separate sources entirely (i.e., one signal may never pass through module  1444 ). 
       FIG. 28  depicts an exemplary logic flow assigning functionality to the various modules of the embodiment of  FIG. 27 .  FIG. 28  depicts the various information/data stored in the memories of the various modules, concomitant with  FIGS. 24A, 24B and 26  detailed above. Is noted that any of the information/data presented in the logic flow diagrams can be information/data stored in the memory of the module. 
     It is noted that while the teachings detailed above have been directed towards the conversion of a middle ear implant from a partially implantable hearing prosthesis to a fully implantable hearing prosthesis, these teachings can be also applicable to other types of hearing prostheses, such as by way of example only and not by way of limitation, cochlear implants and bone conduction devices. In this regard,  FIG. 29  depicts an exemplary functional block diagram of a totally implantable hearing prosthesis in modularized format. Referring back to  FIG. 11  and  FIG. 18 , in an exemplary embodiment, module  1344  is removed or otherwise explanted, and module  1444 X is placed in signal communication with module  1820 , where module  1820  is not removed from the recipient in view of the known risks of explaning and then implanting another cochlear electrode array in the cochlea. Module  1444 X can correspond to module  1444  detailed above, which can correspond to implantable body  744 , except that the sound processor  730  is instead a sound processor for a cochlear implants, and the output of such sound processor is not that which is utilized to drive an actuator, but instead that which is utilized to energize the electrodes of the electrode array. Any of the identification and reconfiguration and adjustments in operation detailed above with respect to the middle ear implant owing to the replacement of one module with another module are applicable to the embodiments associated with  FIG. 29 , at least as those teachings would be modified so as to implement such with a cochlear implant. Indeed,  FIG. 30  depicts an exemplary scenario where the module  1444 X has experienced a failure mode and/or a deactivation mode as detailed above or another variation thereof, or otherwise the recipient has deemed sound captured by an external microphone to be more utilitarian value in a given instance, and thus module  1942  is in signal communication with module  1444 X, the effects of which are the same as or otherwise analogous to those detailed above when module  2342  is utilized in the embodiment of  FIG. 27 . 
     With reference back to  FIG. 20 , it is noted that the teachings detailed herein are applicable to so-called hybrid systems. In an exemplary embodiment, the recipient initially is implanted with a system corresponding to that of  FIG. 6, 7, 8 , or  9  (a middle ear implant). However, as the recipient ages, the ability of the cochlea to evoke a hearing percept based on waves of fluid motions therein for higher frequency sounds becomes degraded. Still, the cochlea remains in a state where it can evoke a hearing percept based on waves of fluid motions therein for the medium and/or lower frequencies sounds. Thus, a decision is made to add a cochlear implant to the existing system. For the exemplary scenario presented herein, it will be assumed that the recipient begins with a partially implantable hearing prosthesis according to  FIG. 6 , with a BTE sound processor utilized as the external component. This is represented by way of block diagrams in a modular form by  FIG. 31 , where module  3142  corresponds to a BTE sound processor, module  3144  corresponds to the receiver unit, and module  3120  corresponds to the intelligent actuator. In this regard,  FIG. 31  corresponds to the embodiment of  FIG. 23 , except that the external component is a BTE device as opposed to a button sound processor. 
     Subsequent to use of the embodiment corresponding to  FIG. 31 , the system is upgraded to a hybrid hearing prosthesis. Modules  3142  and  3144  are removed from the system, and modules  1344  and  1820  are added to the system by way of implantation. Here, module  1344  corresponds to communications unit  644 , except that this communications unit has two outputs or otherwise includes two connectors, one connector for module  1320 , and one connector for module  1820 . Module  1820  corresponds to the stimulator  1020  and electrode array  1030  of  FIG. 11 . Module  3299  is also added, which corresponds to a BTE device configured to serve as an external component of a hybrid prosthesis. 
     Briefly, it is noted that in an alternative embodiment, instead of a communication unit that communicates with both of modules  1320  and  1820 , in an alternate embodiment, two separate communication modules  1344  are provided, as can be seen in  FIG. 33 . 
     In an exemplary embodiment, the external component  3299  is configured to recognize module  1320  and/or module  1820  upon the establishment of signal communication therewith. In an exemplary embodiment, the external component  3299  is configured with logic or otherwise circuitry so as to encode or otherwise manipulate the output such that the lower and/or medium frequency range signals outputted by module  3299  are utilized only by module  1320 , and the high frequency and possibly the medium frequency range signals outputted by module  3299  are utilized only by module  1820  (or at least there is some form of bifurcation of the output, where possible overlap can exist). Concomitant with the teachings detailed above, the external module  3299  can be configured to read or otherwise access memory in the modules  1320  and/or  1820  so as to identify those modules and determine how the output of module  3299  should be managed so that the respective modules operate according to their respective functions vis-à-vis the hybrid arrangement (e.g., evoke a hearing percept at different frequencies). Still further, alternatively and/or in addition to this, the external module  3299  can be configured so that the modules  1320  and/or  1820  can read the memory therein and determine that module  3299  is an external component of a hybrid hearing prostheses so that those modules can operate accordingly. Note also that in some exemplary embodiments, module  1320  and/or module  1820  can be configured to recognize and/or be recognized by the other of module  1320  and/or module  1820 . Such can occur via signal communication through module  1344 A or through modules  1344  and module  3299 . 
     Still, in an exemplary embodiment, a logic circuit within module  3299  can be configured to detect the presence of the module  1820  via the transcutaneous inductance link established with the pertinent communication module. Alternatively, and/or in addition to this, that logic circuit or another logic circuit within module  3299  can be configured to detect the presence of module  1320  via the transcutaneous inductance link established with the pertinent communication module. Upon such detection, the module  3299  can automatically configure itself to operate in a hybrid mode, or more accurately, to output signals so that modules  1320  and module  1820  will operate in the hybrid mode. 
     Any of the techniques detailed herein to enable automatic recognition of one module by another module or otherwise automatic reconfiguration of one module or otherwise automatic change of operation, etc. of a module as a result of that module being placed into signal communication with another module can be utilized in the embodiment of  FIGS. 31 and 32 . 
     Note that while the aforementioned embodiment entailing upgrading to a hybrid system has been directed towards a partially implantable hearing prosthesis, in an exemplary embodiment, such can also be the case with a fully implantable hearing prosthesis. In this regard, the recipient begins with a partially implantable hearing prostheses according to  FIGS. 7  and  14 . This is represented by way of block diagrams in a modular form by  FIG. 14 , as noted above. 
     Subsequent to use of the embodiment corresponding to  FIG. 14 , the system is upgraded to a hybrid hearing prosthesis. Here, a splitter  3410  is added to the connector  610  as seen in  FIG. 34  so as to enable the intelligent actuator  620  and the stimulator  1020  be placed into signal communication with the implantable body  744 .  FIG. 35  depicts the modularized system, where module  3510  corresponds to the splitter  3410 . d    
     Briefly, it is noted that in an alternative embodiment, instead of utilizing a splitter that communicates with both of modules  1320  and  1820 , in an alternate embodiment, two (or more) separate connectors can be provided with respect to module  1444  (implantable body  722 ). Indeed,  FIG. 9  depicts such an exemplary embodiment, albeit where the second connector is connected to the remote microphone/pendant microphone  950 . In this regard, module  1444  could instead be module  1644  of  FIG. 16 , with the appropriate modifications to the sound processor  730  and the addition of a microphone in implantable body  944 . 
     In an exemplary embodiment, module  1444  is configured to recognize module  1320  and/or module  1820  upon the establishment of signal communication therewith. In an exemplary embodiment, the module  1444  is configured with logic or otherwise circuitry so as to encode or otherwise manipulate the output such that the lower and/or medium frequency range signals outputted by module  1444  are utilized only by module  1320 , and the high frequency and possibly the medium frequency range signals outputted by module  1444  are utilized only by module  1820  (or at least there is some form of bifurcation of the output, where possible overlap can exist). Concomitant with the teachings detailed above, the module  1444  can be configured to read or otherwise access memory in the modules  1320  and/or  1820  so as to identify those modules and determine how the output of module  1444  should be managed so that the respective modules operate according to their respective functions vis-à-vis the hybrid arrangement (e.g., evoke a hearing percept at different frequencies). Still further, alternatively, and/or in addition to this, the external module  1444  can be configured so that the modules  1320  and/or  1820  can read the memory therein and determine that module  1444  is an implantable sound processor of a hybrid hearing prosthesis so that those modules can operate accordingly. Note also that in some exemplary embodiments, module  1320  and/or module  1820  can be configured to recognize and/or be recognized by the other of module  1320  and/or module  1820 . Such can occur via signal communication through module  3510  or through module  1444   
     Still, in an exemplary embodiment, a logic circuit within module  1444  can be configured to detect the presence of the module  1820  via signal communication established with the pertinent communication module. Alternatively, and/or in addition to this, that logic circuit or another logic circuit within module  1444  can be configured to detect the presence of module  1320  via the establishment of signal communication established with the pertinent communication module. Upon such detection, the module  1444  can automatically configure itself to operate in a hybrid mode, or more accurately, to output signals so that modules  1320  and module  1820  will operate in the hybrid mode. 
     Any of the techniques detailed herein to enable automatic recognition of one module by another module or otherwise automatic reconfiguration of one module or otherwise automatic change of operation, etc. of a module as a result of that module being placed into signal communication with another module can be utilized in the embodiment of  FIGS. 34 and 35 . 
     It is noted that in an exemplary embodiment, there can be a dedicated output from the implant body  744  in general, and from the signal processor  730  in particular, to the cochlear implant module  1820 , and another dedicated output from the implant body  744  in general, and from the signal processor  730  in particular, to the intelligent actuator module  1320 . Such dedicated outputs can provide audio signals or signals based on audio data to the respective modules. 
     It is noted that in an exemplary embodiment, the implantable body  744  can be configured with a logic circuit that detects the presence of the various modules based on, for example, the characteristic input impedances thereof. 
     It is briefly noted that the embodiment of  FIGS. 34 and 35  can be used in conjunction with an external sound processor as well.  FIG. 36  depicts an exemplary system in modular format including module  3299  in signal communication with module  1444 . Concomitant with the teachings detailed above with respect to a failure mode and/or a deactivation mode of a totally implantable system, or just a desire on the part of the recipient utilizing an external microphone, the external component  3299  can function in a manner analogous to or otherwise the same as the external component detailed above when such component is placed into signal communication with the implantable module including the implantable sound processor. Corollary to this is that module  1444  and/or the other modules of the system of  FIG. 36  can function in a manner analogous to or otherwise the same as the implantable modules detailed above when the external module  3299  and placed into signal communication with module  1444 . 
       FIG. 37  depicts an illustration of the logical flow assigning function to the various modules of the embodiment of  FIG. 36  according to an exemplary embodiment. 
     It is briefly noted that some exemplary embodiments include the utilization of a so-called external programmer. In an exemplary embodiment, the external programmer passes instructions to one or more modules of the implant system or otherwise provides data to one or more modules of the implant system so as to have an efficacious use thereof.  FIG. 38  depicts an exemplary module  3874  corresponding to an external programmer that is placed into signal communication with the implantable module  1444  of the embodiment of  FIG. 35 . In an exemplary embodiment, the external programmer/module  3874  can be configured to provide programming instructions or otherwise data to module  1444 , which then passes that information/data on to module  1820 . In an exemplary embodiment, module  1820  is configured to create a cochlear implant map for the implanted electrodes based on that data. Alternatively, and/or in addition to this, the module  3874  (the external programmer) can provide data or instructions, etc. to the cochlear implant module  1820  so as to add specific parameters to that module, such as by way of example only and not by way of limitation, a group delay adjustment and/or a cutoff frequency etc. 
       FIG. 39  depicts the introduction of module  3874  into the logic flow of  FIG. 37 , were module  3299  is also included for frame of reference. 
     It is noted that while the embodiment of  FIG. 35  is the embodiment in which the external programmer is introduced, it is noted that the external programmer can be applicable to any of the other embodiments detailed herein and/or variations thereof, where the external programmer can have different functionality or otherwise be configured to provide different programming information or data for the other modules present in such embodiments. 
     In view of the above, it is to be understood that at least some exemplary embodiments include an implantable module that is configured to effectively differentiate between other modules placed into signal communication there with. With respect to the above-noted embodiment of the implantable module that has a first functional component, in an exemplary embodiment, the first functional component and implantable speech processor, and the implantable module corresponds to a first module. By way of example only and not by way of limitation, this first module can correspond to module  1444 . Still further by way of example, the first module is configured to automatically recognize that the second module has been placed into signal communication with the first module and recognize the second module is a module having a second functionality of a mechanical tissue stimulator. By way of example only and not by way of limitation, this can correspond to module  1320 . With respect to an exemplary embodiment where the recipient ultimately upgrades to a hybrid of the like, the implantable module can be configured to automatically recognize that a third module has been placed into signal communication with the first module and recognize that the third module is a module having a third functionality of an electric tissue stimulator. By way of example, such can correspond to module  1820 . In an exemplary embodiment, the first module (e.g., module  1444 ) is configured to automatically adjust an operating regime of at least one of the second module of the third module based on the automatic recognition. By way of example only and not by way of limitation, in a scenario where the implantable prosthesis is upgraded to a hybrid, the adjustments of the operating regime could be the adjustment to that of module  1320  such that module  1320  only stimulates at the lower frequencies whereas prior to the adjustments, module  1320  stimulated at all frequencies (low, medium and high frequencies). Corollary to this is that in an exemplary embodiment, the adjustment of the operating regime of the second module of the third module is one that reduces the operational range thereof. Again, in a scenario where recipient is losing his or her high frequency hearing with respect to mechanical stimulation of the cochlea or other tissue, and the third module is a module of a cochlear implant electrode array, the second module would no longer have the operational range across as much of the frequency spectrum as that which was the case prior to the implantation. Corollary to this is that in an exemplary embodiment, the operating regime of the other of the second module of the third module (e.g., in this embodiment, module  1820 ) is one that was encompassed at least in part by the operating regime of the second module prior to the reduction of the operational range. Again with respect to the embodiment where the module  1820  is provided to provide stimulation of the high frequency ranges, module  1820  thus operates in a range that was previously encompassed by that of module  1320 . 
     Continuing with respect to the above-noted embodiment of the implantable module that has a first functional component, in an exemplary embodiment, the first functional component is one of a mechanical tissue stimulator (e.g., a middle ear actuator) or an electric tissue stimulator (e.g., a cochlear implant electrode array). In at least some exemplary embodiments, the implantable module can correspond to a first module, and this implantable module is configured to automatically recognize that a second module has been placed into signal communication with the first module and recognize that the second module is a module having a functionality corresponding to the other of a mechanical tissue stimulator or an electric tissue stimulator. In an exemplary embodiment, with respect to the aforementioned upgrade to the hybrid devices via the addition of module  1820 , in an exemplary embodiment, module  1320  (or the pertinent external module, etc.) can be configured to automatically recognize that module  1820  has been placed into signal communication therewith. Module  1320  is configured to recognize that module  1820  has a functionality different from that of module  1320 . In this exemplary embodiment, this first module (e.g., module  1320 ) is configured to automatically adjust an operating regime of the first functional component (e.g. the actuator) based on the automatic recognition of module  1820 . That said, in an alternate embodiment, the second module can be configured to automatically adjust an operating regime of the second and functional component thereof based on this automatic recognition. 
     Still further, in an exemplary embodiment, the adjustment of the operating regime of the first functional component with a section functional component is one that reduces the operating range thereof. For example, whereas the operational range of the module  1320  could have been stimulating at all frequencies, the adjustments of the operating regime could result in stimulation by module  1320  only at low and/or low and middle frequencies. Still further, the operating regime of the other of the first functional component of the second functional component is one that was encompassed by that of the first functional component with a second functional component prior to the reduction of the operating range. 
     Still with reference to an exemplary embodiment corresponding to a hybrid hearing prosthesis, in an exemplary embodiment, as noted above, there is an exemplary implantable system that includes a first implantable module having a first role in the implantable system, wherein the first implantable module is configured to adopt a second roll automatically upon a changed circumstance. In this exemplary embodiment, the system includes a second module (e.g.,  1320 ) in signal communication with the first module, the second module being an actuator of a mechanical stimulator. The first role of the first module is to receive a first signal based on captured sound having a frequency content including a first frequency content and a second frequency content and provide signals to drive the actuator based on the first signal to evoke a hearing percept at frequencies corresponding to the first frequency content and the second frequency content. In this regard, this can correspond to a scenario where the first module is module  1444  operating in a pre-hybrid mode prior to an upgrade. Still with respect to this exemplary embodiment, the second role can be to receive a second signal based on captured sound having a frequency content including the first frequency content and the second frequency content and provide signals to drive the actuator based on the second signal to evoke a hearing percept at frequencies corresponding to the first frequency content, but not the second frequency content. In this regard, this can correspond to a scenario where the first module is module  1444  operating in the post hybrid upgrade mode, where the module  1444  is bifurcating the frequencies into a component that will be utilized for electrical stimulation via module  1820  and a component that will be utilized for the actuator  1320 . Note also that in this exemplary embodiment, the second module can be a so-called standard actuator, such as the actuator of module  1540 . Thus, in an exemplary embodiment, the second role can also be to provide signals to drive a cochlear implant based on the second signal to evoke a hearing percept at frequencies corresponding to the second frequency content but not the first frequency content. 
     Note also that the utilitarian teachings detailed herein and/or variations thereof can be also applicable to bilateral implants. In this regard,  FIG. 40  depicts an exemplary embodiment of a bilateral hearing prosthesis, having an implantable body  4044  including a sound processor  730  which is in signal communication with three separate connectors  610 . The bilateral hearing prosthesis includes two separate pendulum microphones  950 L and  950 R, each in signal communication with the sound processor  730  via connectors  610 . In an exemplary embodiment, microphones  950 L and  950 R are respectively implanted or otherwise intended to be implanted on the left and right side of the recipient, respectively. Also as can be seen, the intelligent actuator  620  is in signal communication with the sound processor  730 . According to the embodiments where such an embodiment is modularized,  FIG. 41  depicts module  4144 , which corresponds to implantable body  4044 , module  1320 , which corresponds to the intelligent actuator  630  concomitant with the teachings detailed above, module  1650 , which corresponds to microphone  950 R, and module  4150 , which corresponds to microphone  950 L. In an exemplary embodiment, the microphones  950 L and  950 R are intelligent microphones in that the microphones can vary their output based on changing circumstances or otherwise to accommodate a given implantation regime, etc. In an exemplary embodiment, the microphones  950 L and  950 R include memory devices, analogous or otherwise the same as that detailed above, in which data is stored. 
     In an exemplary embodiment, each of the modules  650  and  4150  are initially programmed with information which resides in the memory thereof. In an exemplary embodiment, the memory includes identifying information identifying the microphones as the left side microphone and right side microphone respectively. Still further, in an exemplary embodiment, the memory can include (e.g., in another block thereof) fitting parameters specific to the recipient and the microphone. By way of example only and not by way of limitation, such fitting parameters can include identification of the left or right side, and equalization curve for sensitivity, and/or desired group delay, etc. Any information that has utilitarian value with respect to operating a bilateral prosthesis can be stored in the memory in at least some exemplary embodiments. 
     In view of the above, it is to be understood that at least some exemplary embodiments include an implantable module that is configured to effectively differentiate between other modules placed into signal communication therewith. With respect to this exemplary embodiment, the aforementioned implantable module can correspond to module  4144 , and the functional component can be sound processor  730 . The plurality of different second modules mentioned above can be implantable microphones having recorded therein data indicating which side of the recipient the implantable microphones are implanted. The second modules can correspond to modules  1650  and  4150  detailed above. Still further, the implantable module (e.g., module  4144 ) can be configured to at least one of read the data in the microphones or receive a signal from the microphones with the respective data and adjust operation of the functional component based on the data. In this exemplary embodiment where the functional component is the sound processor, the sound processor will be adjusted so as to take into account the difference in timing between sound being captured on, for example, the left side microphone and sound being captured on for example the right side microphone. In an exemplary embodiment where the actuator module  1320  is implanted such that it provides mechanical stimulation to the recipient&#39;s right side cochlea (where such an exemplary embodiment can also include the actuator that includes a memory in which is located data indicating which side of the recipient the actuator is implanted—indeed, in an exemplary embodiment, module  4144  is configured to at least one of read the data in the actuator and/or receive a signal from the actuator indicating which side the actuator is implanted—that said, in an alternative embodiment, the module  4144  is simply programmed with such data), the sound processor can impart a delay with respect to the input from one of the microphones relative to the other so as to provide a more realistic hearing percept vis-à-vis the fact that one ear will naturally hear a sound originating at one side of the recipient relative to another side of the recipient. 
     In an exemplary embodiment, module  4144  includes a memory unit, concomitant with the other modules with the implantable sound processor detailed above, and the memory can include data corresponding to parameters that take into account the location of the microphones as well as the implanted actuator location. (In this regard, module  1320  can include a memory that includes the implantation side of the actuator (left or right side, etc.)—in an exemplary embodiment, module  4144  is configured to read this memory or otherwise access this memory so as to determine which side the actuator is located on the recipient, and adjust the processing regime of the signal processor accordingly.) In an exemplary embodiment, module  4144  is configured to read the memories of the microphones to determine which microphones are located on which side of the recipient, and adjust the processing regime of the sound processor accordingly. 
       FIG. 42  depicts an illustration of the logical flow assigning functions to the modules of the embodiment of  FIG. 41 , wherein external sound processor  3299  has been added to that system. Note also that the module  4144  can include data associated with the side on which the implantable sound processor is located. Such can have utilitarian value with respect to evaluating how to process the signals from the left and right microphones. In this regard, if the module  4144  does not know which side is implanted on, the information regarding the fact that a given microphone is implanted on the left or right side may not be utilitarian. Because the memory of the module  4144  includes data relating to the side of the recipient on which is implanted, the module  4144  can evaluate the signals based one such data. Corollary to this is that in an exemplary embodiment, the data stored in the implantable module  4144  can correspond to the side on which the tissue stimulator is implanted. Such can have utilitarian value in that that can have a significant driver on how the signals are processed. Note also that in an exemplary embodiment, module  4144  can include both information relating to the side of the recipient on which the module is implanted, and the side of the recipient on which the tissue stimulator is located. Such can have utilitarian value with respect to a module  4144  that includes an integral microphone (as opposed to a remote microphone) in a manner analogous to the utilitarian value of knowing which sides of the recipient the pendulum microphones are implanted. 
     Still with reference to an exemplary embodiment corresponding to a bimodal hearing prosthesis, in an exemplary embodiment, as noted above, there is an exemplary implantable system that includes a first implantable module having a first role in the implantable system, wherein the first implantable module is configured to adopt a second roll automatically upon a changed circumstance. In this exemplary embodiment, the first implantable module includes a sound processor, and the first role is a role of a sound processor that processes sound captured by the implantable microphone only on a first side of the recipient. The second role is a role of the sound processor that processes sound captured by an implantable microphone on a second side of the recipient. Note that in this exemplary embodiment, the second role can also include processing sound captured by the implantable microphone on the first side of the recipient. 
     It is noted that the teachings detailed herein are also applicable to external acoustic hearing aids, whether or not such be part of a hybrid system, such as the embodiment of  FIG. 20  detailed above, or as part of a standalone system. 
     It is noted that some exemplary embodiments of the systems detailed herein are such that sound streaming from an external source can utilize the same communications protocol as that for the external microphone. That said, in some alternate embodiments, a different communications protocol is utilized for streaming sounds than that utilized for the external microphone. Accordingly, by way of example only and not by way of limitation, at least one of the implantable modules is configured to recognize whether or not an external module in signal communication therewith is providing streaming sound data and/or sound data captured from a microphone, and adjust the functionality thereof accordingly. Note also that some exemplary embodiments utilize different frequencies other than the communications frequency to recharge the implantable battery(s). In such an exemplary embodiment, this can enable concurrent charging and sound streaming. Accordingly, an exemplary embodiment can determine whether or not a recharging module or the like is in signal communication with the implanted modules detailed herein and adjust the functionality of such modules accordingly. An exemplary change in the functionality thereof could be adjusting the internal circuitry so as to be receptive to the different frequencies utilized by the battery charger. 
     In view of the above, it is to be understood that some exemplary embodiments include exemplary methods utilizing the teachings detailed herein. In this regard,  FIG. 43  depicts an exemplary flowchart representing method  4300 . Method  4300  includes method action  4310 , which entails operating an implantable component as part of a partially implantable prosthesis based on a first receive signal by the implantable component. In an exemplary embodiment, this can entail operating the intelligent actuator  620 /the module  1320 . In an exemplary embodiment, this can entail operating those components as part of the embodiment depicted in  FIG. 31 . The first received signal can be a signal from the implanted receiver unit  644 /module  1344 . Still further, method  4300  includes method action  4320 , which entails automatically operating the implantable component as part of a fully implantable prosthesis based on a second received signal by the implantable component. In an exemplary embodiment, the second received signal can be a signal sent from the implantable body  744 /the module  1444 . In this exemplary embodiment, this method action  4320  can occur when the intelligent actuator  620 /the module  1320  is part of the system of  FIG. 34 . In an exemplary embodiment, the automatic operation of the implantable component (e.g., the intelligent actuator) can occur because the intelligent actuator is configured to analyze the output of the module  1444  and determine that it is not an RF signal such as that which would be the case with respect to output from the module  1344  during method action  4310 , but instead a signal from a sound processor  730 . In an exemplary embodiment, the automatic operation of the implantable component can occur, because the intelligent actuator received a signal (the second signal) from the module  1444  indicating that the module  1320  should operate as part of a fully implantable prosthesis, or at least should operate in a manner where the module  1320  receives stimulation/drive signals and actuates accordingly (e.g., the module  1320  operates in the slave mode noted above). In an exemplary embodiment, the automatic operation of the implantable component can occur because the intelligent actuator received a signal from the module  1444  indicating that the signals provided thereto are provided from an implantable sound processor, and thus logic or otherwise programming in the intelligent actuator is such that the intelligent actuator is configured to reconfigure itself to operate accordingly. Still further, in an exemplary embodiment, the second received signal is a result of an interrogation by the module  1220  of the module  1444  when module  1444  is placed into signal communication with module  1320 . For example, the second received signal can be the results of the module  1320  reading the memory of module  1444 . 
     Again, the operation of the implantable component as part of a fully implantable prosthesis occurs automatically based on the second received signal. This is as distinguished from a scenario where the surgeon or the like modifies or otherwise adjusts the operation of the implantable component prior to operation thereof. 
     In an exemplary embodiment, the action of operating the implantable component as part of a partially implantable prosthesis is executed prior to the action of operating the implantable component is part of a fully implantable prosthesis. In an exemplary embodiment, such a temporal regime corresponds to that which would result from upgrading a partially implantable hearing prosthesis to a fully implantable hearing prosthesis. 
     Referring now to  FIG. 44 , it can be seen that there is a flowchart for an exemplary method  4400 , which includes method action  4410 , which entails executing method  4300 . Method  4400  further includes method action  4420 , which entails, subsequent to the actions of operating the implantable component as part of a fully implantable prosthesis, operating the implantable component as part of a partially implantable prosthesis based on a third received signal by the implantable component. In an exemplary embodiment, such can occur by way of example only and not by way of limitation, as a result of a failure mode and/or a deficiency mode associated with the implantable components of the hearing prosthesis as detailed above (e.g., a failed component, reduced battery power/discharged battery, a recipient desires to utilize an external microphone, etc.). Continuing with the exemplary embodiment where the implantable component is the intelligent actuator  620 /the module  1320 , such automatic operation can be a result of any of the aforementioned scenarios, albeit in reverse (e.g., the module  1320  receives an RF signal, and module  1320  is configured to recognize that it should operate in the intelligent actuator mode because it is receiving an RF signal; module  1320  receives instructions for module  14442  operate in the intelligent actuator mode, etc.). 
     Concomitant with the concept of operating the implantable component as part of a partially implantable prosthesis even though the prostheses is configured to operate in the fully implantable mode (albeit circumstances prevent such), in view of the above, it is to be understood that the action of operating the implantable component as part of a partially implantable prosthesis based on the third receive signal can be executed automatically by the implantable component based on an analysis of a state of the system by the implantable component and executed while the structure for a fully implantable prosthesis is implanted in the recipient. This analysis of the state of the system can be based on an analysis of the third signal received by the implantable component. Also concomitant with the exemplary embodiments detailed above, the second received signal can be a signal from a second implantable component (e.g., module  1444 ) having an implantable microphone (e.g., microphone  740 ) and/or in signal communication with an implantable microphone (e.g., microphone  950 ). Still further, the action of operating the implantable component as part of a fully implantable prosthesis is executed automatically upon an analysis of the second received signal by the implantable component. 
     Still, in an exemplary embodiment, there is any of the methods detailed above and/or below, wherein at least one of: (i) the second implantable component is configured to embed a code in the received signal indicating that the second signal is from a component that enables the implantable component to operate as part of a totally implantable configuration (e.g., module  1444  embeds a signal into a stimulator/driver signal output therefrom); or (ii) the implantable component is configured to extrapolate from the second signal the source thereof and determine that the second signal is from a component that enables the implantable component to operate as part of a totally implantable configuration (e.g., the input to module  1320  is not an RF signal/the input to module  1320  is stimulator/driver signals, and thus the module  1320  recognizes that it should operate in the aforementioned standard mode/slave mode, etc.). 
     It is noted that in an exemplary embodiment of method action  4300 , the implantable component is an implanted sound processor in wired communication with an implanted microphone. In this regard, in an exemplary embodiment, this can be the case where method action  4310  corresponds to the scenario where there is been a failure mode or a deficiency mode where the recipient seeks to utilize an external microphone, etc. 
     As noted above, there is an exemplary implantable system that includes a first implantable module having a first role in the implantable system, wherein the first implantable module is configured to adopt a second roll automatically upon a changed circumstance. An exemplary embodiment includes a method action comprising surgically implanting at least a portion of the system that includes the first implantable module. In this exemplary method, the first implantable module adopts the second roll automatically during the implantation process upon the establishment of signal communication with a second implantable module. It is noted that by “surgically implanting a system,” that action need not include the action of implanting the first implantable module. In this regard, the first implantable module can be already implanted (e.g., such could be the module  1320 , etc.). 
     As detailed above, the various modules include recorded or otherwise stored therein data. It is noted that in an exemplary embodiment, any one or more of the modules detailed herein and/or variations thereof where generic model in general is configured to at least one of transmit at least a portion of the data stored in the memory to another module or enable another module to read at least a portion of the data stored in the memory. In an exemplary embodiment, the data stored in the memory can correspond to any of the data detailed herein and/or variations thereof. In an exemplary embodiment, the system utilizing the innovative modules detailed herein and/or variations thereof utilizes the data so as to reconfigure a given module or otherwise adjust the operation of the given module or otherwise change the role of a given module, etc., according to the teachings detailed herein. 
     It is noted that any device and/or system detailed herein also corresponds to a disclosure of a method of operating that device and/or using that device. Furthermore, any device and/or system detailed herein also corresponds to a disclosure of manufacturing or otherwise providing that device and/or system. Corollary to this is that any disclosure of a method herein corresponds to a disclosure of a device and/or system of implementing that method and/or a program product for implementing that method on a computer apparatus. Still further, any functionality of any device and/or system detailed herein corresponds to a method of taking action to achieve such functionality. 
     Any teaching of any embodiment detailed herein can be combined with one or more of other teachings of other embodiments detailed herein, providing that the art enables such, unless otherwise specified. It is further noted that any particular one or more teachings detailed herein can be omitted from an embodiment when implementing some exemplary embodiments. To be clear, any feature detailed herein can be combined with any other feature detailed herein unless otherwise noted, and/or unless the prior art does not enable such. 
     While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. It will be apparent to persons skilled in the relevant art that various changes in form and detail can be made therein without departing from the spirit and scope of the invention.