SYSTEMS AND METHODS FOR PATIENT-ENABLED BLADDER CONTROL

Abstract

A system for controlling urination in a patient includes an implantable controller and an external device. The implantable controller includes circuitry and electrodes for stimulating the pudendal nerves in order to control urination. In addition, the implantable controller includes sensors for determining information on bladder fullness and for transmitting such information to an external device which is used for controlling the implanted controller. The external device will display when bladder filling exceeds a safe threshold level, allowing the patient and a caregiver to take appropriate steps to allow the patient to urinate.

Claims

1. A system for controlling urination in a patient unable to voluntarily control urination, said system comprising: at least two implantable electrodes configured to deliver current to the patient's pudendal nerve(s) in the form of an electrical waveform, wherein the electrodes are disposed in or on an atraumatic cuff configured to fit over a branch of the patient's pudendal nerve, the cuff including a resilient material configured to grip and remain in place on the pudendal nerve after implantation; an implantable sensor configured to sense information corresponding to a degree of filling of the patient's bladder; an implantable controller configured to concurrently deliver at least a first and second electrical waveform to said at least two implantable electrodes, the first and second electrical waveforms configured to stimulate and block the patient's pudendal nerve to cause at least a first and second physiological action involved in voiding of the bladder; an external device configured to receive information from the implantable sensor corresponding to a degree of bladder filling, display a value corresponding to the degree of filling, and to send a signal to the implantable controller to initiate voiding of the bladder.

2. The system of claim 1, wherein the controller is configured to concurrently deliver the at least a first and second electrical waveforms.

3. The system of claim 1, wherein the at least a first and second electrical waveforms are charged balanced.

4. The system of claim 1, wherein the electrodes positioned on the cuff comprise bipolar electrodes.

5. The system of claim 1, wherein the electrodes positioned on the cuff comprise tripolar electrodes including a positive and two ground electrodes configured to minimize leakage of current outside of the cuff.

6. The system of claim 1, wherein the cuff exerts no more than about 100 mmg of pressure on the pudendal nerve.

7. The system of claim 1, wherein the cuff exerts no more than about 0.5N of force on the pudendal neve.

8. The system of claim 1, wherein the cuff includes a circumferential gap configured to allow the cuff to be placed over the pudendal nerve.

9. The system of claim 1, wherein the at least two implantable electrodes comprise a first and second electrode, which are configured to be implanted to deliver current to the same branch of the pudendal nerve.

10. The system of claim 10, further comprising a third electrode, wherein the third electrode is configured to be implanted to deliver current to a contralateral branch of the pudendal nerve relative to the branch to which current is delivered by the first and second electrodes.

11. The system of claim 10, wherein the third electrode is configured to deliver a high frequency waveform configured to open the patient's urinary sphincter to allow urination.

12. The system of claim 1, wherein the first electrical waveform comprises a low frequency waveform configured to contract the patient's bladder and the second waveform comprises a high frequency waveform configured to open the patient's urinary sphincter to allow urination.

13. The system of claim 12, wherein the low frequency waveform has a frequency in a range of about 10 to 50 Hz.

14. The system of claim 12, wherein the high frequency waveform has a frequency in a range of about 4 to 10 kHz.

15. The system of claim 12, where the first and second electrical wave forms have a voltage of about 5V, and a current in a range of about 0.1 to 15 mA.

16. The system of claim 12, wherein the low frequency electrical waveform is delivered through a first electrode and the high frequency waveform is delivered through a second electrode.

17. The system of claim 16, further comprising a third electrode configured to deliver a third electrical waveform, wherein the high frequency electrical waveform is delivered by a second electrode configured to deliver current to a contralateral branch of the pudendal nerve relative to the branch of the pudendal nerve to which current having a low frequency waveform is delivered by the first electrode.

18. The system of claim 12, wherein the controller is configured to initiate delivery of the high frequency waveform before the low frequency waveform so to open the urinary sphincter before bladder contraction occurs.

19. The system of claim 12, wherein the controller is further configured to selectively deliver a very low frequency electrical waveform to relax the patient's bladder.

20. The system of claim 19, wherein the very low frequency waveform has a frequency in a range of about 1 to 10 Hz.

21. The system of claim 1, wherein the implantable sensor is configured to measure at least one of bladder pressure, bladder wall stretch, or bladder distension.

22. The system of claim 1, wherein the implantable sensor is configured to measure at least one of bladder pressure, bladder wall stretch, or bladder distension.

23. The system of claim 22, wherein the implantable sensor is a strain gauge.

24. The system of claim 1, wherein the external device initiates voiding by sending a signal to the implantable controller to deliver a low frequency electrical waveform to the pudendal nerve to contract the bladder and a high frequency electrical waveform to the pudendal nerve to open the urinary sphincter to allow urination.

25. A method for controlling urination in a patient unable to voluntarily control urination, said method comprising: providing a control system having an ability to sense information on bladder fullness signal and signaling the information to an external device configured to provide the patient an indication of bladder fullness, the system further configured to enable the patient or caregiver to selectively stimulate the patient's pudendal nerve to initiate voiding of the bladder; determining information of bladder fullness and signaling the information to the external device, the external device being configured to wirelessly communicate with an implanted controller including a pulse generator to generate electrical waveforms and at least a first and second implanted electrode positioned in electrical contact with a first or second branch of the pudendal nerve, the at least a first and second electrodes electrically coupled to the controller to receive the electrical waveforms; and utilizing the information of bladder fullness to deliver the electrical waveforms to the pudendal nerve to selectively stimulate and/or block the pudendal nerve to initiate voiding of the patient's bladder and urination by causing physiological actions involved in the urination process, wherein the least a first and second electrodes are disposed in an atraumatic cuff positioned over the first or second branch of the pudendal nerves, the cuff including a resilient material configured to grip and remain in place on the pudendal nerve after implantation.

26. The method of claim 25, wherein a high frequency electrical waveform is delivered to the pudendal nerve to block the nerve so as to cause opening of the urethra.

27. The method of claim 26, wherein the high frequency electrical waveform has a frequency in a range of about 4 to 10 kHz.

28. The method of claim 25, wherein a low frequency electrical waveform is delivered to the pudendal nerve to stimulate the nerve so as to cause contraction of the bladder.

29. The method of claim 28, wherein the low frequency electrical waveform has a frequency in a range of about 10 to 50 Hz.

30. The method of claim 28, wherein after completion of the delivery of the low frequency wave form, a very low frequency electrical waveform is delivered to the pudendal nerve to stimulate the nerve so as to cause relaxation of the bladder so at to cease urination.

31. The method of claim 30, wherein the very low frequency electrical waveform has a frequency in a range of about 1 to 10 Hz.

32. The method of claim 25, wherein the information on bladder fullness comprises at least one of bladder pressure, bladder wall stretch, or bladder distension.

33. The method of claim 25, wherein the information on bladder fullness is calibrated to the patient.

34. The method of claim 25, wherein the information on bladder fullness is sensed by a pressure sensor, bladder distention sensor or bladder wall stretch sensor.

35. The method of claim 25, wherein the second pudendal nerve branch is a contralateral branch to the first pudendal nerve branch.

36. The method of claim 25, wherein the cuff exerts no more than about 100 mg of pressure on the pudendal nerve or no more than about 0.5N of force.

37. The method of claim 25, wherein the electrical waveforms comprise at least a first and second waveform to cause at least a first and second physiological action involved in the urination process.

38. The method of claim 37, wherein the first electrical waveform comprises a low frequency waveform configured to stimulate the patient's pudendal nerve to contract the patient's bladder and the second waveform comprises a high frequency waveform configured block the patient's pudendal nerve to open the patient's urinary sphincter to allow urination.

39. The method of claim 38, wherein the low frequency waveform has a frequency in the range of about 10 to 50 Hz.

40. The method of claim 38, wherein the high frequency waveform has a frequency in the range of about 4 to 10 kHz.

41. The method of 38, wherein the low frequency electrical waveform is delivered through the first implanted electrode and the high frequency waveform is delivered through the second implanted electrode.

42. The method of claim 37, wherein a third electrical waveform is delivered to the patient's pudendal nerve to stimulate or block the patient's pudendal nerve.

43. The method of claim 42, wherein the third electrical waveform is a very low frequency waveform configured to stimulate the patient's pudendal nerve to cause relaxation of the bladder so at to cease urination so as to cease urination.

44. The method of claim 43, wherein the very low frequency waveform has a frequency in a range of about 1 to 10 Hz.

45. The method of claim 43, the very low frequency wave form is delivered after completion of the delivery of the low frequency wave form, so as to cause relaxation of the bladder so at to cease urination.

46. The method of claim 42, wherein the third electrical waveform is delivered by a third implanted electrode positioned in contact with the first or second branch of the pudendal nerve and electrically coupled to the controller.

47. The method of claim 46, wherein third electrode is implanted to be in electrical contact with a contralateral branch of the pudendal nerve relative to the branch to which the first and second implanted electrodes are in electrical contact with.

48. The method of claim 47, wherein the third electrode delivers an electrical waveform to block the pudendal nerve to open or keep open the patient's urinary sphincter, the first electrode delivers an electrical waveform to stimulate the pudendal nerve to contract or relax the patient's bladder, and the second electrode delivers an electrical waveform to block the pudendal nerve to open or keep open the patient's urinary sphincter.

49. The method of claim 48, wherein the electrical wave form to the block the pudendal nerve to open or keep open the urinary sphincter is a high frequency waveform, the electrical waveform to contract the bladder is a low frequency signal, and the electrical waveform to relax the bladder is a very low frequency waveform.

50. The method of claim 25, wherein the control system includes an implantable controller connected to the pudendal nerve by at least two electrodes and an external device configured to wirelessly communicate with the implanted controller.

51. The method of claim 50, wherein the indication of bladder fullness provided to the patient is in the form of a visual display, visual alarm or audio alarm generated by the external device.

52. The method of claim 50, wherein the patient or caregiver receives the indication from the external device and initiates voiding through an interface on the external device.

53. The method of claim 52, wherein initiating voiding via the external device causes the implantable controller to contract the bladder and open the patient's urinary sphincter.

54. The method of claim 53, further comprising: the patient or caregiver stopping bladder voiding by sending a signal from the external device to the implantable controller to relax the bladder.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0024] FIG. 1 illustrates a prior art system for selectively stimulating the pudendal nerves to control urination taken from US Patent Publication No. 2014/0249595, the full disclosure of which has previously been incorporated herein by reference. In particular, FIG. 1 depicts a three-channel system for stimulating pudendal nerves or branches thereof to perform one or more functions in the urination process. Pulse generator 10 is depicted as having three output channels. Wire leads 12 and 13 are attached to electrodes 14 and 15, which are placed about pudendal nerve 20. Electrode 15 is shown distal to electrode 14. In the context of a method comprising blocking the EUS and/or anal sphincter and stimulating or inhibiting contractions in the bladder and/or rectum, electrode 14 would be used to stimulate or inhibit bladder and/or rectal contractions, while electrode 15 would be used to block the EUS or anal sphincter. As needed, wire lead 16 is attached to another electrode (not shown in FIG. 1) that is placed about the pudendal nerve on the other side of the body to block the pudendal nerve on the opposite side. Pulse generator 10 is shown as implanted beneath skin 40. Output parameters of the pulse generator 10 can be controlled via a wired interface, but preferably are controlled by wireless transmission, which can be carried using any suitable wireless protocol, such as radio frequency, IEEE 802.11a/b/g, Bluetooth®, etc. Thus, in the embodiments of FIG. 1, an external controller 30 is depicted for communicating with the pulse generator 10. External controller 30 is depicted as having a display 32, such as an LCD, LED or OLED display, and a keypad 34 for entering data into the external controller 30. External controller is depicted as sending a wireless transmission 36 to pulse generator 10, though in another embodiment, data can be transferred both to the pulse generator 10 from the external communicator 30 and vice-versa, to permit monitoring of one or more parameters of pulse generator 10, including, without limitation, output signal characteristics (e.g., frequency, amplitude, etc. as outlined above) and battery strength. Activity of pulse generator 10 and external controller 30 typically is microprocessor controlled and software/firmware installed onto the pulse generator 10 and external controller 30 hardware may be used to implement the described tasks, and to provide, for example and without limitation, a GUI (graphical user interface) for the display 32, which facilitates use of the system. Both pulse generator 10 and external controller 30 may comprise any suitable electrical and electronic components to implement the activities, including, microprocessors, memory (e.g., RAM, ROM. Flash memory, etc.), connectors, batteries, power transformers, amplifiers, etc.

[0025] FIG. 2 is a schematic illustration showing normal innervation of the urinary tract.

[0026] FIG. 3 is a schematic illustration showing the system components of the present invention including the implanted components, the components of the external device and the optional connections to a power source and to a computer or other programming source.

[0027] FIG. 4 is a schematic illustration showing an embodiment of positioning of the implantable electrodes on the left and right pudendal nerve.

[0028] FIGS. 5a and 5b are lateral view showing an embodiment of a cuff configured to be placed over a branch of the pudendal nerve (FIG. 5a); and placement of the cuff over a branch of the pudendal nerve (FIG. 5b).

[0029] FIGS. 6a and 6b are lateral and cross sectional views showing an embodiment of a bipolar electrode the positioning of the electrode on the electrode cuff placed over a branch of the pudendal nerve.

[0030] FIGS. 7a and 7b are lateral and cross sectional views showing an embodiment of a tripolar electrode the positioning of the electrode on the electrode cuff placed over a branch of the pudendal nerve.

[0031] FIG. 8 is a block diagram illustrating certain method steps according to the present invention.

DETAILED DESCRIPTION OF THE INVENTION

[0032] Embodiments of the invention provide devices, systems and methods for delivering stimulating signals to paralyzed and other patients incapable of voluntary control of urinary function. Many embodiments provide the stimulating signals to these patients in the form of electrical currents so as to so as to initiate and/or control their urinary function. In particular embodiments, systems of the present invention provide both an external device and an implanted device which are capable of working in combination to allow a patient to selectively control urinary function by stimulating the pudendal nerve to initiate urination and optionally to terminate urination. Also in particular embodiments, the present invention provides real time information relating to the patient's bladder fullness, usually by measuring and indicating pressure but optionally, by measuring and indicating bladder distension or stretching of the bladder wall.

[0033] The system components for initiating and optionally terminating urination may be generally the same as those described in the systems of U.S. patent publication 2014/0249595, which has previously been incorporated herein by reference herein for all purposes. The systems of that patent publication, however, provide no means for giving a patient feedback or information relating to bladder fullness, making it more difficult for the patient to determine when to urinate. Moreover, the systems of that patent publication rely on dedicated external controllers where all system components are dedicated and intended for use only in controlling the disclosed systems.

[0034] As many embodiments of the invention relate to approaches for controlling urinary function, particular for patients who are paralyzed and/or who are otherwise incapable of voluntary control of urinary function a brief explanation will now be presented of the neural circuitry for control of the urinary function and what happens as result of spinal cord injury. Referring now to FIG. 2, the neural circuitry that controls the urine voiding process is complex and highly distributed: it involves pathways at many levels of the brain, the spinal cord and peripheral nervous system and is mediated by multiple neurotransmitters. The two goals of normal bladder function are to store urine until there is a socially acceptable time and place and to empty the bladder in a coordinated fashion. The act of voiding is primarily controlled by the parasympathetic nervous system, primarily via the pelvic nerve (S2-S4); whereas, storage is primarily accomplished via the sympathetic nervous system (specifically at T10-L2, hypogastric nerve) which increases urethral closure pressure and inhibits parasympathetic nerves to the bladder as shown in FIG. 2. When the path between the sacral micturition center and the brain is intact, voiding is coordinated and occurs by relaxation of the striated (external) urethral sphincter, contraction of the detrusor, and opening of the bladder neck and urethra. When the path between the brain and the sacral micturition center is damaged or disrupted (e.g., by spinal cord injury) the coordination between detrusor and sphincter during voiding is impaired in a condition known as Detrusor-sphincter dyssynergia or DSD. DSD is commonly characterized by involuntary contractions of the external urethral sphincter during an involuntary detrusor contraction. Sequelae of DSD include hydronephoris, recurrent pyelonephritis, and renal failure. DSD is caused by neurological lesions between the brainstem and the sacral spinal cord and specific causes of DSD include: traumatic spinal cord injury, multiple sclerosis, spinal dysraphism, and transverse myelitis.

[0035] Referring now to FIG. 3, a system 100 constructed in accordance with the principles of the present invention typically comprises both an implantable controller 102 and an external controller 120. Though in some embodiments, it may only include an implantable or external controller. The implantable controller 102 will be of the type intended for long-term implantation and will have at least first and second electrodes 104 and 106 intended for connection to at least one branch of the pudendal nerves PN1 and PN2. Typically, electrodes 104 and 106 are configured for connected to the same pudendal nerve PNI. Optionally, a third electrode 108 will be provided, typically for connection to a contralateral branch of the pudendal nerves PN2. According to one or more embodiments, third electrode 108 can be configured to be used by controller 120 to deliver a current to stop or otherwise inhibit bladder contraction so as to stop urination. It may also be used as to block the pudendal nerve to open or keep open the urinary sphincter.

[0036] Of particular interest to the present invention, the system 100 will typically further include a bladder fullness sensor 110, which may correspond any one or more of those sensors described earlier, including for example, pressure sensors, bladder distension sensors, bladder wall stretch sensors, and the like. One or more of these sensors may correspond to strain gauges includes MEMS based strain gauges known in the art. According to various embodiments sensor 110 can be positioned on or adjacent the bladder wall. Further the sensor may have an atraumatic biocompatible coating or layer (e.g., silicone or polyurethane) configured to minimize irritation of the bladder wall including that causing any type of wound healing response (e.g., collagen or cellular deposition or the like) so as to minimize any changes to the mechanical properties to the section of the bladder wall to which the sensor is attached. This may also be accomplished through the size and shape of the sensor 110. Desirably, sensor 110 has a rounded shape so as to minimize any stress applied to the wall on its edges and also has a stiffness of less than equal to the bladder in various states of distention. The purpose of these sensors will be to sense information corresponding to a degree of bladder fullness to determine when the bladder has reached a threshold level of fullness as it is filled through the ureters UR from the kidneys (not shown). In various embodiments, the information collected by sensors 110 can calibrated against the patient themselves by taking another measurement of bladder pressure during a set amount of bladder filling using a foley catheter or other like device and bladder pressure measurement method known in the art. As discussed earlier, overfilling of the bladder can back urine into the kidneys through the ureters presenting substantial risk of morbidity and mortality to the patient. Thus in use, embodiments of the invention employing sensors 110 can reduce the risk of back flow of urine into the kidneys and the associated risk of morbidity and mortality to the patient including that caused by kidney damage.

[0037] The implantable controller 102 will include a microprocessor 112 for managing the functions of the controller, including controlling a stimulator or pulse generator 114 to deliver stimulation energy to the electrodes 104, 106, and optionally 108. The microprocessor 112 will further be connected to an antenna 116 which provides transmission capability to the implantable controller for wirelessly communicating with the external controller 120. Usually, the antenna 116 will be designed to operate at a radio frequency (RF) suitable for transcutaneous communication. In particular embodiments, the antenna can be configured to operate in the MICS frequency range known in the art. Optionally, the antenna 116 may further be configured to receive energy from a suitable RF source to be stored in an on-board battery (not shown) or other energy storage means known in the art (e.g., a capacitor or super capacitor) in a conventional manner. Alternatively, the implantable controller may be configured to run on non-rechargeable batteries requiring periodic battery replacement. In various embodiments, antenna 116 may be a tuned or tunable antenna may have a variety of shapes such as the coiled shaped as shown in FIG. 3 as well as straight, square, rectangular or other like shape, with the length or other dimension selected for transmission at particular frequency or range of frequencies. Further in particular embodiments, antenna 116 or other antenna described herein may be a stub antenna and/or a stub tuned antenna.

[0038] The external controller 120 may be a relatively simple controller of the type described in US Patent Publication No. 2014/0249595, modified only to receive bladder fullness data from the implanted controller and to display such data on the display screen of that external device. Preferably, however, the external controllers on the present invention will be a combination or assembly including both a shell component 124 and a conventional personal digital assistant (PDA) of a type commonly available. As used herein, reference to a personal digital assistant (PDA) will mean any small, mobile, usually hand-held device that is able to provide computing and storage information and retrieval capabilities. The PDA's use in the present invention will include at least a body, display, a user interface, wireless communication capability, a rechargeable battery, and a power port for recharging the rechargeable battery, and usually for also transmitting data to and from other external devices, such as computers, tablets, cell phones and the like. The wireless communication capability can be in the form of an RF communication device e.g., an RF communication chip configured to communication in a BLUETOOTH or other related format. Exemplary PDA's at the present time include “smart phones,” of the type sold by Apple Computer, Samsung, and others. In the future, such smart phones may further evolve and may be identified by different names, but it is expected that they still will be compatible with the external control components of the present invention.

[0039] Referring again specifically to FIG. 3, the shell 124 has a receptacle region 126 which can slidingly receive the PDA so that a power/data port 122 on the PDA is able to mate or otherwise engage with a power/data plug 128 on the shell at the bottom of the receptacle region 126. In alternative embodiments, receptacle region 126 can be configured to receive the PDA by means of a snap or press fit over the PDA or by a joining means such as use of VELCRO or a releasable adhesive. In these and other embodiments, the receptacle region 126 is aligned and otherwise configured such that, when the PDA is fully inserted, the plug 128 will be fully inserted into the port 122. In use, such embodiments allows for a complete electrical and data connection between the PDA and the accessory device without the user having to manipulate plug 128 or the receptacle region 126. Further as described above, this can be achieved by the sliding movement alone of the PDA into the receptacle region 126 and/or by the action of snapping or pressing the PDA into the receptacle region 126 and/or pressing the receptacle region over the PDA. Such alignment for plug 128 can be achieved by control of the tolerances of the receptacle region 126 and/or plug 128, and/or the use of guiding structures or other guiding means (not shown) on the receptacle region and/or receptacle region 126 and/or plug 128. It will be appreciated that the plug 128 will typically be identical to the plug which is provided by the vendor of the PDA and intended for recharging the PDA and/or exchanging data with the PDA and the computer, tablet, or other external device. However, in other embodiments, plug 128 may not necessarily be the same as the plug on the PDA and may be configured to attach to an adaptor to connect to the plug on the PDA. In various embodiments, plug 128 may correspond to any of the USB connectors known in the art including, for example, USB A, USB B, USB Micro A, USB Micro B, USB Mini A and USB Mini B. In particular preferred embodiments, plug 128 may correspond to a USB Type C connector including for example a USB 3.1 Type C connector. In use, use of a USB type C or other like connectors for plug 128 including USB 3.1 allows for one or more of the following: i) easier connection and faster data transmission (e.g., up to about 10 Gbps.) between logic units 136 and one or more controllers associated with the PDA, like device or external computer; ii) faster and more complete charging of battery 134 (including an input power of up to 100 watts at 20 Volts); and iii) compatibility with a greater number of PDA's, like devices or an external computer.

[0040] According to one or more embodiments of shell 126, plug 128 will be connected to a further port 130 at the bottom of the shell by a coupling bridge 132. At a minimum, the coupling bridge will provide electrical connections so that when a vendor-supplied plug 148 on cable 126 (intended to be plugged directly into port 128 on the PDA) is plugged into the port 130, the PDA will see all connections as if the plug 148 were plugged directly into the port 128. In addition, the coupling bridge 132 will provide a number of capabilities to the circuitry within the shell 124. At a minimum, the coupling bridge 132 will be connected to a rechargeable battery 134 which is part of the shell so that the rechargeable battery 134 will be maintained fully charged so long as the PDA is being used and is plugged in via the port 130.

[0041] In many embodiments, the coupling bridge 132 will usually be connected to provide a data link to a processor or other logic unit 136 which is part of the shell 124 and which controls communication of the shell with the implantable controller 102. Logic unit 136 may also correspond to one or more of an Application Specific Integrated Circuit (ASIC), state device/machine, analogue device or other logic means known in the art. The processor or logic unit 136 will be connected (directly or operably) with an antenna 138 which is specifically configured to communicate with the antenna 116 which is part of the implantable controller 102. Usually, both antennas 116 and 138 will be configured for radio frequency transmission at a range selected to operate transcutaneously. Commonly, the antennas are coil-like devices, but other antenna configurations may be provided (e.g., a stub antenna). Optionally, the antenna and logic unit 136 may include a further antenna 142 intended for digital communication with the PDA and/or other external digital devices. Data communication between the PDA and the processor logic unit 136 may thus be effected via the coupling bridge 132, via the digital antenna 142 or both. Typically digital antenna 142 is an RF based antenna configured for Blue Tooth communication with the PDS, however it may configured for other frequency ranges outside the Blue Tooth protocol may also be used. For example, in particular embodiments, one or more of antennas 116, 138, 142 and logic unit 136 may be configured to communicate within the Medical Implant Communication Service (MICS) frequency band, typically between 402 and 405 MHz, though other frequencies are also considered.

[0042] Once the PDA is fully inserted into the shell 124, the combination of the PDA and the shell will be configured to be used as a single unit with the patient and/or caregiver entering commands and data using the PDA interface, typically touch screen 121, and data being shown on the same display 121. Optionally, data may be entered by speech recognition means on the PDA and alarms and other signals may be provided by an audio capability of the PDA.

[0043] In normal operation, the implantable controller 102 will be continuously or periodically monitoring bladder fullness using the sensor 110 and information regarding bladder fullness (e.g., an amount of bladder stretching or distension (absolute or percentage), an amount of bladder fullness (absolute or percentage) or bladder pressure) will continuously or periodically be transmitted via the microprocessor 112 and antenna 116 to the PDA via antenna 138 and the processing logic unit 136.

[0044] In some cases, it will be desired only to recharge the PDA and battery 134 of the shell 124 where the cable 146 may be plugged into the wall through a power supply 150. Alternatively, when it is desired to reprogram the PDA, the unit may be plugged into a personal computer 154 via a USB plug 152 which goes into the USB port 156 on the computer.

[0045] Referring now to FIG. 4, in specific embodiment electrodes 104, 106 are connected to the left pudendal nerve and electrode 108 to the right pudendal nerve. Electrode 104 can be used to send very low frequency electrical waveforms (typically g. 1 to 10 hz) to stimulate the pudendal nerve to keep the bladder relaxed or a low frequency wave forms to open the bladder (e.g., 10 to 50 hz). Electrode 108 is used to send high frequency waveforms (e.g., 4 to 20 kHz) to block the right pudendal nerve (typically from natural nerve impulses) to open or keep the urinary sphincter EUS. Electrode 106 is also used to send a high frequency signal to block the left pudendal nerve (e.g., from waveforms from electrode 104) so as to open or keep open the urinary sphincter.

[0046] Referring now to FIGS. 5-7 in various embodiments one more of electrodes 104, 106 and 108 can be positioned on a cuff 200 configured to fit over and remain on branch of the pudendal nerve. The electrodes 104, 106 and 108 can be positioned so as to have a radial or axial orientation in relation to the cuff 200. The cuff 200 will usually have a circumferential opening 202 to allow to cuff to be fit over the pudendal nerve by the doctor. Cuff 200 is desirably fabricated from elastic materials such as silicone or urethane and has sufficient radial spring force to clamp down on and remain on the pudendal nerve once so placed. At the same time the dimensions and mechanical and material properties of the cuff are such that it desirably exerts not more than about 150 mm of pressure on the pudendal nerve or about 0.5 Newtons of force as forces below this amount serve to maintain the health of the pudendal nerve. Also the cuff 200, including its inner surface 201 are desirably constructed from atraumatic biomaterials such as one or more of silicone, polyurethane, TEFLON, and the like so as to be atraumatic to the pudendal nerve including the pudendal nerve sheath. The inner surface of cuff 200 may include one more drug eluting coatings known in the art to improve the biocompability of the coating and reducing any inflammation or tissue adherence at the interface of the cuff with the pudendal nerve. Desirably cuff 200 is also constructed from insulative materials so as to prevent the leaking of any current outside of the cuff and thus prevent unwanted stimulation or block of another portion of branch of the pudendal nerve.

[0047] Referring now to FIGS. 6a and 6b in various embodiments one more of electrodes 104, 106 and 108 can be figured as bi-polar electrodes 220 having a positive and negative pole or portion 221 and 222 which may be positioned radially or axially around cuff 200. Referring to now to FIGS. 7a and 7b, in still other embodiment one or more of electrodes 104, 106 and 108 can be configured as tri-polar electrodes 230 having a positive pole or portion 231 and negative portions 232. In use embodiments of such a tripolar electrodes 230 serve to reduce the leakage of any current outside of cuff 200 and in turn reduce unwanted stimulation or blockage of a given branch of the pudendal nerve or a surrounding branch.

[0048] Referring now to FIG. 8, an embodiment of a method for utilizing an embodiment of system 100 to control urination along with an algorithm 300 for doing so will now be illustrated. Algorithm 300 may be implemented by an electronic instruction set (which may be in the form of a software module 301) resident on microprocessor 112 or other logic resources contained in controller 102 and/or on logic unit 136 or other logic resources on PDA/controller 120. In a first step 310, the implanted sensor and controller to transmit bladder filling/information (e.g., in the form of bladder pressure, wall distention or wall stretch data), either continuously or periodically to the PDA or a combination of both. So long as the bladder is not filled (event 311), the PDA can display that status or can simply display nothing. In the event that the signal indicating bladder filling exceeds a threshold level (event 312); however, the PDA will present an alert or alarm to the patient or caregiver in step 320. The alarm may be a visual one displayed in various graphic forms on the display screen. Alternatively, the alarm may be audible via a small speaker on the PDA, or in some cases the alarm or alert may be both visual and audible. After receiving the alert or alarm, the patient or caregiver knows that the bladder should be emptied (e.g., by urination) in order to prevent over pressure of the bladder and potential damage to the kidneys. The patient or caregiver then has time to go to a lavatory or obtain the appropriate receptacles to collect the urine during urination. After appropriate preparation step 330, the caregiver can use the PDA to signal the implanted controller to provide appropriate signals to the pudendal nerves in order to initiate urination in step 340. Useful stimulation frequencies, currents and voltages for achieving a selected result are presented below in Table 1. In specific embodiments the current can range from about 0.1 to 14.9 mA, with a preferred embodiments of about 1 to 14 ma and more preferably in range of about 1 tolmA. It should be appreciated that embodiments of the invention are not limited to these value, but rather other values are considered as well. It should also be appreciated that for these and other values and parameters cited herein, the term “about” means within +/−10% of a stated value for a dimension, characteristic, physical property and the like.

TABLE-US-00001 TABLE 1 Bladder Stimulation Parameters Stimulation Current Stimulation Frequency Voltage Site Result 0.5 to 15 Hz; <15 mA; 50 V Pudendal Nerve Relax preferred, to Bladder lO Hz, preferred value of 5 Hz 10 to 50 Hz; <15 mA; 50 V Pudendal Nerve Contract preferred 20 Hz Bladder Above 4 kHz, 4 to <15 mA; 50 V Contralateral Inhibit 30 kHz, preferred Pudendal nerve Contraction 4 to 20 kHz, more of Urinary preferred 4 to Sphincter 10 kHz, preferred to open value of about 6 kHz sphincter

[0049] According to one embodiment, urination can be allowed to terminate as a result of complete voiding of the bladder and the stimulatory signals can be terminated at that time. Alternately, the PDA and an implanted controller may be utilized to send a signal in step 340 to relax the bladder which will terminate urination even if the bladder is not completely voided. After urination is terminated, the patient and caregivers may continue with other activities and rely on the systems of the present invention to again alert them when bladder filling has exceeded the allowable threshold level. In various embodiments, delays can be built into the system between the time the patent signals for voiding and the voiding waveform is sent as well as between the time between when the waveform is sent to stop voiding after the patient signals it (e.g., using the PDA). The delays can be in the tenths of seconds or longer.

[0050] The foregoing description of various embodiments of the invention has been presented for purposes of illustration and description. It is not intended to limit the invention to the precise forms disclosed. Many modifications, variations and refinements will be apparent to practitioners skilled in the art. For example, embodiments of the device can be sized and otherwise adapted for various pediatric and neonatal applications as well as various veterinary applications. They may also be adapted for the urinary tracts of both male and females. Further, those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, numerous equivalents to the specific devices and methods described herein. Such equivalents are considered to be within the scope of the present invention and are covered by the appended claims below.

[0051] Elements, characteristics, or acts from one embodiment can be readily recombined or substituted with one or more elements, characteristics or acts from other embodiments to form numerous additional embodiments within the scope of the invention. Moreover, elements that are shown or described as being combined with other elements, can, in various embodiments, exist as standalone elements. Hence, the scope of the present invention is not limited to the specifics of the described embodiments, but is instead limited solely by the appended claims.