DE112008003193T5 - Arrangement of connected microtransponders for implantation - Google Patents

Abstract

A microtransponder array, comprising: an array composed of adjacent and physically connected wireless microtransponders; each microtransponder having a wireless interface.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of Provisional Patent Application 61 / 079,004, filed on Jul. 8, 2008, and 60 / 990,278, filed on Nov. 26, 2007, which is hereby incorporated by reference. It is a continuation-in-part of non-provisional application 10 / 741,136 filed December 19, 2003 and application 61 / 088,774 filed August 14, 2008, which are also incorporated herein by reference. This application may be related to the present application or may merely share some drawings and / or a portion of the disclosure.

HTNTERGRUND

The numerous innovative teachings of the present application will be described with particular reference to a number of embodiments, including presently preferred embodiments (by way of example and not limitation), as well as other embodiments.

A variety of medical conditions include disorders of the nervous system in the human body. These conditions may include paralysis due to spinal injury, cerebral palsy, poliomyelitis, sensory loss, sleep apnea, acute pain, etc. A characteristic feature of these disorders can z. For example, it may be the inability of the brain to communicate neurologically with the nervous systems distributed throughout the body. This may be a consequence of physical disruptions within the body's nervous system and / or chemical imbalances that may alter the ability of the nervous system to receive and transmit electrical signals, such as those that propagate between neurons.

Advances in the medical field have produced techniques aimed at restoring or rehabilitating neurological deficiencies leading to some of the above-mentioned conditions. However, these techniques are usually directed at the treatment of the central nervous system and thus quite invasive. These techniques contain z. For example, implanting devices such as electrodes into the brain and physically connecting these devices via wires to an external system designed to send and receive signals to and from the implanted devices. Although the incorporation of foreign bodies into the human body is useful, it usually produces various physiological complications, including surgical wounds and infection, which make these techniques very challenging to implement.

For example, the size of the implanted devices and the wires therefrom may reduce or substantially limit patient motion. In addition, unavoidable patient movement may cause the implanted device to shift, resulting in patient discomfort and possibly inoperability of the implanted device. Thus, corrective invasive procedures may be necessary to reposition the device within the body, further increasing the risk of infection or other complications.

In addition, an implanted device typically requires a battery for operation, and if the device is to remain in the body for extended periods of time, the batteries must be replaced, requiring additional intervention that can lead to further complications. In addition, certain applications require that the implanted devices be miniaturized as much as possible so that they can be accurately implanted into the human body or that a group of them can be implanted within a small defined range.

The publication US20020198572 von Weiner describes z. B. a device for providing a subcutaneous electrical stimulation. The device is certainly useful because it provides pain relief by stimulating peripheral nerves, thus avoiding interference with the target of the brain or central nervous system (CNS). However, the device is bulky and has wire leads connecting the power sources to the implanted electrode.

Techniques like those in the US Publication 20030212440 by Boveja and related patents avoid the problem of battery replacement in a biostimulator using a magnetic transmit coil (RF transmit coil) placed over the area of the body containing the implanted electrodes. This coil receives power and command signals via inductive coupling to generate stimulation pulses to activate motor units. Since the device does not include a battery, the electrical power is dissipated from the externally generated RF field in the transmit coil. However, the device is specifically designed for the stimulus of the cranial nerve and not generally applicable. Furthermore, the disclosed device still has a substantial implant device with leads that connect the electrodes (along the cranial nerve) with the implanted stimulus receptor (in the chest).

Another approach is followed in devices similar to those used in the US Publication 20030212440 described by Boveja that were made under the trademark BION ^® and at present are for the treatment of urinary incontinence and headaches in clinical trials. The BION ^® units are quite large, ranging from about 2 mm x 10 mm x 2 mm (thickness), with much smaller embodiments are preferred for implantation. In addition, BION ^® units must be hermetically sealed to protect the coils from the damaging effects of water and other bodily fluids. Furthermore, BION ^® units require relatively high levels of externally applied RF power (often> 1 Watt) to provide the higher stimulus currents, which are required for their main purpose for active stimulation of individual muscles or muscle groups.

The US Publication 20050137652 by Cauller et al. creates small, wireless nerve stimulators. In this disclosed device, a plurality of single channel electrodes have an interface with cell matter and thus allow smaller devices to be used without sacrificing effectiveness. Because the subdermal tissue conducts electrical signals, despite the small size of the devices and the distance from the nerve, the small electrodes can provide sufficient signal to stimulate neurons.

The US publication 20060206162 Wahlstrand et al. also describes a device that is capable of transcutaneous stimulation with an array of electrodes attached to the skin surface at the back of the neck. However, this device contains a battery within the housing and is still quite large.

VeriChip ^® is the first FDA-approved human-implantable RFID microchip. The device, about twice the length of a grain of rice, is encapsulated in glass (to seal the internal components to the body) and is implanted over the area of the triceps on a person's right arm. When sampled at the correct frequency, the VeriChip ^® answers with a unique sixteen-digit number that can correlate the user with information stored in a database for identification purposes, medical record access, and other purposes. The data is not encrypted, which causes serious privacy concerns, and there is some evidence that the devices can cause cancer in mice.

The clinical function of an electronic device such as a micro-transponder, pacemaker leads, neurostimulation leads, or other electrical leads depends on the device being able to maintain close anatomical contact with the target tissue (usually nerve or muscle tissue). All foreign substances implanted in the body undergo a foreign body reaction from the surrounding host tissues. The body recognizes the implant as foreign, causing an inflammatory response followed by encapsulation of the implant with fibrous tissue (or glial tissue - called gliosis - if in the central nervous system). The injury to the anatomical structures and to the tissue surrounding the implant during implantation of the device may also result in scarring (fibrosis or gliosis). Finally, after successful implantation, fiber encapsulation of the device may occur if the device is manipulated (some patients are constantly fingering a subdermal / subcutaneous implant) or irritated by the patient's daily activities.

When scarring occurs around the implanted device, the electrical characteristics of the electrode-tissue interface degrade and the function of the device may fail clinically significant. For example, additional electrical power from the lead may be required to overcome the additional resistance imposed by the intervening scar. One of the observed error of VeriChip ^® -Entwurfs is that it because it is integrated with the surrounding tissue, requires that the surgeon impeccably good meat surgically removed.

SUMMARY

There are advantages to using even smaller, more reliable wireless implantable devices and / or methods that are designed to treat nerve or other biological disorders and address the above-mentioned disadvantages, including easy implantation and removal.

An embodiment of a wireless microtransponder includes an assembly. The assembly may include a removably connected array of embedded and interconnected microtransponders, allowing for easy removal of the assembly with minimal surgical invasion. An implantable device can be more easily removed after acute treatment or even in the event of a disorder or patient paranoia. This invention may allow for easier removal of the actual microtransponder. In some In embodiments, the design may include an array of dedicated single microtransponders so that a surgeon may access and remove the assembly rather than individual microtransponders.

• – Kleine Größe, die mehrere Stimuli innerhalb eines kleinen Bereichs zulässt.
• – Leichtigkeit der Implantation, da die Anordnung die Implantation unter Verwendung einer Nadel zulässt.
• – Leichtigkeit der Entfernung, da die feste Anordnung verbundener Mikrotransponder im Vergleich zu einzelnen Mikrotransponder leichter extrahiert werden kann.
• – Verringerte invasive Eingriffe für Implantation und Entfernung.

In various embodiments, the disclosed innovations provide one or more of the following advantages:

• - Small size that allows multiple stimuli within a small range.
• Ease of implantation as the assembly permits implantation using a needle.
• Ease of removal, since the fixed arrangement of connected microtransponders can be extracted more easily compared to individual microtransponders.
• - Reduced invasive procedures for implantation and removal.

BRIEF DESCRIPTION OF THE DRAWING

The disclosed inventions will be described with reference to the accompanying drawings, which illustrate important exemplary embodiments of the invention and which are hereby incorporated by reference into the description, wherein:

1 Figure 3 is a functional diagram of a complete microtransponder for sensing and / or stimulating nerve activity in accordance with the present innovations.

2 is an illustration of a laminar spiral microcoil used in the construction of a microtransponder platform for stimulating nerve activity in accordance with the present innovations.

3 FIG. 4 is an illustration of a laminar spiral microcoil that has been electroplated on a substrate in accordance with the present innovations.

4 an illustration of a circuit diagram for a wireless microtransponder, which is designed for the independent self-triggering operation (asynchronous stimulation), in accordance with the present innovations.

5 provides several graphs summarizing how the stimulus rate, the stimulus current peak amplitude and the stimulus pulse duration of a wireless microtransponder vary under different device settings and input conditions of external RF power in accordance with the present innovations.

6 an illustration of a circuit diagram for a wireless microtransponder with an external trigger signal demodulator for synchronizing the delivered stimuli with a plurality of other wireless microtransponder in accordance with the present innovations.

7 Fig. 4 is a diagram illustrating the demodulation of a differential interrupt trigger signal in accordance with the present innovations.

8th provides several graphs summarizing the results of tests of a wireless microtransponder (with a demodulator element for triggering an external interruption) under various device settings and conditions of the strength of the external RF power in accordance with the present innovations.

9A an illustration of a deployment of multiple wireless microtransponders distributed throughout subcutaneous vascular beds and nerve terminalis fields in accordance with the present innovations.

9B an illustration of using wireless microtransponders to enable coupling with deep microtransponder implants is in accordance with the present innovations.

9C an illustration of using wireless microtransponders to enable coupling with deep nerve microtransponder implants is in accordance with the present innovations.

10 an illustration is how wireless micro-transponders can be employed using a beveled rectangular hypodermic needle in accordance with the present innovations.

10A Figure 5 is an illustration of the present innovation for the use of connected microtransponders that are used for subcutaneous injection using a beveled rectangular needle.

11 Figure 11 is an illustration of a manufacturing sequence for helical type wireless microtransponders in accordance with the present innovations.

12A a perspective view of the basic embodiment of an arrangement shows.

12B a side view of the basic embodiment of an arrangement shows.

12C a plan view of the basic embodiment of an arrangement shows.

13A shows a perspective view of an arrangement comprising electrodes exposed by windows in the array.

13B Fig. 10 shows a side view of an arrangement comprising electrodes exposed by windows in the array.

13C shows a top view of an arrangement comprising electrodes exposed by windows in the array.

14A shows a perspective view of an arrangement comprising an ion-permeable strip.

14B a side view of an arrangement comprising an ion-permeable strip.

14C shows a plan view of an arrangement comprising an ion-permeable strip.

15A a perspective view of a slotted arrangement shows.

15B a side view of the slotted arrangement shows.

15C a top view of the slotted arrangement shows.

16A shows a perspective view of an arrangement which is surrounded by an enveloping matrix.

16B shows a side view of an arrangement surrounded by a shell matrix.

16C shows a plan view of an arrangement which is surrounded by an envelope matrix.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The numerous innovative teachings of the present application will be described with particular reference to the presently preferred embodiment (by way of example and not limitation).

Various embodiments of the present invention are directed to the miniaturization of minimally invasive wireless micro-implants, called "microtransponders," which may be small enough to allow numerous independent microtransponders to be implanted under a square inch of skin to sample a variety of biological signals To stimulate variety of tissue reactions. The microtransponders can operate without implanted batteries or wires by receiving electromagnetic power from flexible coils placed on the surface of the overlying skin. The microtransponder design relies on radio frequency identification (RFID) devices with wireless technology.

The present application discloses new approaches to methods and apparatus for providing minimally invasive wireless microtransponders that can be subcutaneously implanted and configured to sense a set of biological signals and / or to stimulate a variety of tissue responses. The microtransponders contain miniaturized micro-coils that are formed using new manufacturing techniques, and have simplified circuit designs that minimize the overall size of the microtransponders. The unprecedented miniaturization of minimally invasive biomedical implants, made possible with this wireless microtransponder technology, would allow new forms of distributed stimulation or high resolution scanning using micro-implants that are so small that implant densities of 100 per square inch of skin are possible.

The simplicity of the microtransponder allows for extreme miniaturization and allows many micro-transponders to be implanted in a given area, usually by relatively non-invasive injection techniques. The micro-transponder are biologically compatible, thus avoiding the necessity of sealing the devices (as with the VeriChip ^®) and further contribute to a small size. Many biocompatible materials and coatings such as gold, platinum, SU-8, ^Teflon® , polyglycerols or hydrophilic polymers such as polyethylene glycol (PEG) are known. In addition, many materials can be biocompatible by passivating the surface to render it inert. In some embodiments, the microtransponder may include a migration-inhibiting coating, such as a porous polypropylene polymer, to prevent migration away from the site of implantation. However, experiments so far show that the uncoated devices do not migrate. These small devices float independently in the tissue and only move as the tissue moves, thus minimizing tissue rejection and encapsulation and maximizing longevity and effectiveness.

Wireless RFID technology involves near-field magnetic coupling between two simple coils that are tuned to resonate at the same frequency (or have a harmonic that matches one harmonic or the fundamental frequency of the other coil). Throughout this document, references to tuning two coils to the same frequency include adjusting the frequencies of the coils at the fundamental and / or harmonic frequencies.

Electromagnetic radio frequency (RF) power applied to one of these coils creates a field in the space around that power coil. In any remote coil placed within this power field, electrical power can be remotely induced as long as the remote coil is properly tuned to resonate at the same frequency as the power coil.

In the microtransponder, a miniaturized helical micro-coil optimized for near-field induction can be used. The microcoil includes a nonconductive substrate, a conductive coil, and a photoresist layer patterned over the conductive coil, the microcoil being electroplated on the nonconductive substrate. The microcoil can be used to both receive and transmit wireless signals, such as a wireless power or wireless data signal.

Power may be externally supplied using near-field coupling to provide electrical stimulation via a PDA-like programmable controller that allows the user to control the electrical parameters as needed for a given physiological condition. Near field coupling means that the external driver needs to be close to the micro-transponder (eg, about 1 cm away), but by adding coils or increasing the size (to some point), increased distance can be achieved. Protection against interference with other external RF sources is achieved in part by the short distance between the power source and the microtransponder, but the use of a selected frequency and an encrypted connection between the external and internal system allows implant activation by external RF sources further reduced.

A self-triggering wireless microtransponder can be used to provide asynchronous electrical stimulation. The microtransponder of this embodiment includes a resonator element, a rectifier element, a stimulus voltage element, a stimulus discharge element and a conductive electrode. The micro-transponder is configured to discharge an electrical stimulus at a repetition rate controlled by the strength of the externally applied RF power field.

A wireless microtransponder with an external trigger signal demodulator element may be used to provide synchronized electrical stimulation. The microtransponder of this embodiment includes a resonator element, a rectifier element, an external trigger pulse demodulator element, a stimulus timer element, a stimulus driver element, and a conductive electrode. The external trigger pulse demodulator element is configured to receive a trigger signal from an external high frequency power field (RF power field). The stimulus driver element is configured to discharge an electrical stimulus when the external trip pulse demodulator element receives the trigger signal.

1 Figure 4 is a functional schematic of a complete microtransponder for sensing and / or stimulating nerve activity in accordance with one embodiment. The circuit is designed for the dependent tripping operation (synchronous pacing). The circuit 10 contains electrical components that are designed as an electrical interface with neurons of peripheral nerves. Furthermore, the circuit contains 10 electrical components that allow the microtransponder to interact wirelessly with systems external to the microtransponder. These systems may include other body-implanted transponders or external coils and / or a receiver. The wireless capabilities of the circuit 10 allow the delivery of electrical signals to and / or from the peripheral nerves. These include electrical signals indicative of nerve tip signals and / or signals configured to stimulate peripheral nerves distributed throughout the subcutaneous tissue.

Accordingly, the circuit contains 10 around a central axis 12 wound microcoil 22 , The microcoil 22 is to a capacitor 11 and a switch 15 to an RF identity modulator 17 connected in parallel. The HF identity modulator 17 is with an RF identity and RF trigger pulse demodulator 13 coupled, in turn, with a rectifier 14 is coupled. The rectifier 14 is with a tip sensor trigger 16 and with a stimulus driver 20 coupled. The rectifier 14 and the top sensor 16 Both are a capacitor 18 connected in parallel. Besides, the top sensor is 16 with a nerve tip electrode 19 coupled and thereby electrically connects the tip sensor 16 with nerve conduction tissue (neurons). Similarly, the nerve stimulus electrode connects 21 the stimulus driver 20 with nerve conduction tissue (axons). The top sensor 16 consists of one or more junction field effect transistors (JFETs). As one of ordinary skill in the art will appreciate, the JFET may include metal oxide semiconductor field effect transistors (MOSFETs).

The sensors, drivers, and other electronic components described in the present application can be fabricated using standard high integration (VLSI) techniques. Further, the tip sensor 16 with the RF identity modulator 17 which is adapted to receive an incoming / RF carrier signal in response to the tip sensor 16 recorded nerve spike signals modulated. In one embodiment, the nerve electrodes (ie, the nerve tip electrode 19 and the nerve stimulus electrode 21 ), with which the peak sensor 16 or the stimulus driver 20 is connected, bundled and configured as an interface with the nerve conduction portion (axon portion) of a peripheral nerve.

A like through 1 As shown, the configuration of the above devices allows the microtransponder to operate as an autonomous wireless unit that can detect peak signals generated by peripheral nerves and relay those signals to external receivers for further processing. Of course, the microtransponder performs these operations while being powered by external RF electromagnetic signals. The abovementioned abilities are facilitated by the fact that magnetic fields are not easily attenuated by human tissue. This allows the RF electromagnetic signals to sufficiently penetrate the human body so that signals can be received and / or transmitted by the micro-transponder. In other words, the microcoil 22 is for magnetic interaction with the RF field whose magnetic flux is within that of the microcoil 22 surrounding space varies, designed and configured. Because the micro-coils 22 If they are conductors, they convert the fluctuations of the magnetic flux of the external RF field into alternating electrical currents that are inside the micro-coil 22 and the circuit 10 flow. The alternating current is z. B. in the rectifier 14 passed, which converts the alternating current into direct current. The DC power can then be used to charge the capacitor 18 be used, whereby a potential difference across the JFET of the tip sensor 16 is produced.

In an exemplary embodiment, a gate of the tip sensor 16 JFET across the nerve tip electrode 19 be coupled to the nerve transmission tissue (neurons). The gate of the tip sensor 16 JFET may be chosen to have a threshold voltage that is within a voltage range of those signals generated by the nerve axons. In this way, the gate of the tip sensor becomes 16 during peak phases of the nerve axons open, causing the circuit 10 closes. When the circuit 10 closes, the external RF electromagnetic field generates an LC response in the coupled induction coil 22 and the capacitor 18 which then resonate with the external RF electromagnetic field, with their resonance matched to the modulation frequency of the RF electromagnetic field. The LC characteristic of the circuit 10 and the threshold voltage of the gate of the tip sensor 16 JFETs can be chosen to be within the coupled microcoil (ie the induction coil) 22 and the capacitor 18 a unique modulation is determined, thereby providing an identification signal for the microtransponder. Accordingly, the tip sensor 16 JFET for the RF identity modulator 17 a unique trigger signal for generating desired RF signals ready. The identity signal may indicate the nature of the nerve activity in the vicinity of the microtransponder, as well as the location of nerve activity within the body as derived from the specified identified microtransponder position.

It should be appreciated that the RF capabilities, as above in terms of the circuit 10 has been discussed, can make the microtransponder a passive device that responds to incoming RF carrier signals. That is, the circuit 10 does not actively emit any signals but rather reflects and / or scatters the electromagnetic signals of the RF carrier wave to provide signals with a specific modulation. The circuit picks up 10 Power from a high-frequency carrier wave (RF carrier wave) to the electrical components that make up the circuit 10 to provide power.

Although the in 1 can be used to receive signals from the micro-transponder in response to peak signals generated by peripheral nerves, other components of the circuit 10 of the microtransponder include components for stimulating the peripheral nerves using the external RF signals. For example, those through the microcoil 22 received RF signals via the RF identity and RF tripping pulse demodulator 13 be converted into electrical signals to provide sufficient current and voltage for the stimulation of the peripheral nerves. Thus, the RF identity and RF trigger pulse demodulator conducts 13 Power off from an RF carrier signal to the stimulus driver 20 With Supplying power that provides electrical signals suitable for the stimulation of nerve conduction tissue (axons). This can be used to treat nerves that are damaged or otherwise physiologically deficient. Because of the nature of the identification signal, a microtransponder can be selectively activated to provide electrostimulation.

Of course, in certain embodiments, the minimum size for the microtransponders may be limited by the size of the micro-inductor responsible for power induction, and secondly by the size of the capacitors necessary to tune the power storage and timing. In fact, micro-coil designs with a diameter of less than 1 millimeter and only a few microns thick can provide sufficient wireless power to drive the complex integrated circuits, which can be much smaller than these coils. The combination of the sophisticated functionality of microelectronic chips with the wireless performance of these microcoils produces the smallest possible minimally invasive tiny patches as small as ~ 0.1 mm thick and ~ 1 mm wide. These economies of scale and performance make it possible to add relatively complex digital electronics to the smallest transponder.

2 Figure 4 is an illustration of a laminar spiral microfilm power circuit used in the construction of a microtransponder platform for stimulating nerve activity in accordance with one embodiment. As shown here, the microtransponder contains a laminar spiral microcoil (L _T ) 202 that with a capacitor (C _T ) 204 coupled, in turn, with a microelectronics chip 206 is coupled. The microelectronics chip 206 includes a power capacitor element 208 that with a capacitor element (C _DUR element) 210 coupled, in turn, with a nerve stimulation chip element 212 is coupled. In an exemplary embodiment of the microtransponder platform, the microcoil is not more than 500 μm long by 500 μm wide and is the combined thickness of the laminar spiral microcoil (L _T ). 202 , of the capacitor (C _T ) 204 and the microelectronic chip 206 not more than 100 μm.

3 FIG. 10 is an illustration of a laminar spiral microcoil electroplated on a substrate in accordance with an embodiment. FIG. As shown in the drawing, power lines are initially 302 electroplated in a tight spiral pattern on an unreactive substrate (eg, glass, silicon, etc.). In one embodiment, the laminar spiral micro-coil may be power lines 302 included, which are about 10 microns wide, with the distance 304 between the power lines is set to about 10 microns. In a further embodiment, the laminar spiral micro-coil can power lines 302 included, which are about 20 microns wide, with the distance 304 between the power lines 302 is set to about 20 microns. However, the widths of the power line 302 and the conductor distance 304 of course, they should be set to any value as long as the resulting microcoil can produce the desired induced current for the desired application.

A platinum-iridium alloy is the preferred plating material for forming the power lines 302 , Other acceptable conductors used to form the power lines 302 can be used are gold or platinum.

In certain embodiments, when the spiral microcoil has been electroplated on the substrate, a polymer based layer is spin coated on the microcoils to provide a protective layer against corrosion and disintegration after implantation. Long-term studies on animals with SU-8 implants have demonstrated the biocompatibility of the plastic SU-8 by demonstrating that these SU-8 implants remained functional for the duration of these studies, with no evidence of tissue reaction or material degradation. Thus, the polymer-based layer usually comprises a plastic SU-8 or an equivalent type having a thickness of approximately 30 μm.

4 13 is an illustration of a circuit diagram for a wireless microtransponder configured for independent self-timer operation (asynchronous pacing), in accordance with one embodiment. As the circuit diagram shows, the self-triggering microtransponder contains a resonator element 404 (ie "parallel resonant circuit"), a rectifier element 406 , a stimulus voltage element 408 , a stimulus discharge element 410 and one or more electrodes 412 , The resonator element 404 contains a coil component (L _T component) 403 provided with a capacitor component (C _T component) 407 is coupled. The resonator element 404 is configured to operate at a precise frequency, which depends on the values of these two components (ie the coil component 403 and the capacitor device 407 ), as described in Equation 1: F _res = I / (2π√LC)

The resonator element 404 is with the rectifier element 406 coupled, in turn, with the stimulus voltage element 408 and with the stimulus discharge element 410 is coupled. The Rectifier element 406 and the stimulus voltage element 408 Both are a capacitor 411 connected in parallel. In addition, the stimulus is unloading element 410 with electrodes 412 coupled, causing the stimulus discharge element 410 is electrically connected to nerve conduction tissue (axons). It should be appreciated that in certain embodiments immediately after the rectifier element 406 a voltage boosting device (not shown) may be included to provide the supply voltage available for stimulation and for operation of the integrated electronics beyond that provided by the miniaturized LC 'parallel' resonant circuit 404 in addition to increase limit values. This voltage booster circuit can enable electro-stimulation and other microtransponder operations using the smallest possible LC devices that can generate too low voltages (<0.5V). Examples of high efficiency booster circuits include charge pumps and switch booster circuits using low threshold Schottky diodes. However, any type of conventional high efficiency voltage booster circuit may, of course, be used in this capacity as long as it can produce the voltage required for the particular application of the microtransponder.

In this circuit configuration, the self-triggering microtransponder can be a bistable silicon switch 416 Use it to switch between the charging phase on the stimulus capacitor 411 builds up a charge, and the discharge phase, by closing the state of the switch 416 for discharging the capacitor 411 via the stimulus electrodes 412 can be triggered when the charge reaches the desired stimulation voltage to oscillate. To regulate the stimulus frequency by limiting the charge rate becomes a single resistor 413 used. The breakdown voltage of a single Zener diode 405 is configured to by discharging the current and triggering the closing of the switch 416 what the capacitor 411 on the electrodes 412 (Gold or platinum-iridium alloy) discharges the desired stimulus voltage when it reaches the stimulation voltage. Although initial gold was considered to be the preferred electrode material, it was recognized that gold salt deposits could form during long-term implantation and form a microbattery that interferes with the stimulus signal. For some applications, gold remains a viable electrode material, but platinum-iridium alloy is considered to be the preferred embodiment for long-term long-term use. Platinum is another acceptable electrode material.

The stimulus peak amplitude and duration are largely independent of the applied RF power level by the effective tissue resistance (eg, skin 414 , Muscle, fat, etc.). However, increasing the RF power may increase the pacing rate by reducing the time required to charge to the stimulus voltage.

The self-triggering microtransponder operates without clock signals from the RF power source (RF power coil) 402 and independently "triggers" the repetitive stimulation "self". As a result, the stimulation generated by a plurality of such self-triggering microtransponders is dependent on that produced by each transponder circuit 404 induced effective transponder voltage from one stimulator to another in terms of phase asynchronous and slightly variable in frequency. Although unique to this technology, there is no reason to predict that distributed asynchronous pacing would be less effective than synchronous pacing. In fact, such asynchronous pacing is more likely to produce the nature of disordered "pins and needles" or "excited quivering" sensations of paresthesia associated with pacing methods that most effectively block pain signals.

5 16 shows several graphs illustrating how stimulus frequencies, stimulus current peak amplitudes, and wireless microtransponder stimulus durations vary according to various device settings and external RF power input conditions, in accordance with an embodiment. In the first graphic representation 502 the external RF power input is set to 5 mW, resulting in a stimulus frequency of 4 Hz. As previously discussed, the stimulus rate is a function of RF power since it directly affects the time taken to charge the stimulus voltage. This direct relationship between RF power and stimulus frequency is clear in the graph 502 in comparison to the graphic representation 504 see where the external RF power increases from 5 mW to 25 mW, resulting in a significant increase in the stimulus frequency from 4 Hz to 14 Hz. However, these are of course only examples of how the RF power input settings affect the stimulus frequency. In practice, the effects of the RF power input setting on the stimulus frequency may be increased or decreased depending on the particular application (eg, depth of implantation, proximity of interfering body structures such as bones, organs, etc.) and device settings.

While the RF power controls the stimulus frequency, the stimulus voltage is usually controlled by the transponder diode diode element. Furthermore, the effect of the stimulus voltage on the stimulus current peak amplitude and on the pulse duration is determined by the resistive properties of the tissue surrounding the microtransponder.

6 13 is an illustration of a circuit diagram for a wireless microtransponder having an external trigger signal demodulator element for synchronizing the delivered stimuli with a plurality of other wireless microtransponders in accordance with an embodiment. As shown here, the design of the wireless transponder is off 5 changed so that it is a demodulator element 608 for an external trigger signal so that the stimulus discharge can be synchronized by a trigger signal from an external RF power field.

The modified circuit includes a resonator element 604 , a rectifier element 606 , a demodulator element 608 for an external trigger, a stimulus timer element 610 , a stimulus driver element 611 and one or more electrodes 612 , The resonator element 604 contains a coil component (L _T ) 601 that with a capacitor component (C _T ) 607 is coupled. The resonator element 604 is configured to operate at a precise frequency that depends on the value of these two devices (ie, the coil device 601 and the capacitor device 607 ), as described in Equation 1.

The resonator element 604 is with the rectifier element 606 coupled, in turn, with the demodulator element 608 for an external trigger, with the stimulus timer element 610 and with the stimulus driver element 611 is coupled. The rectifier element 606 and the stimulus timer element 608 are both to the capacitor 607 connected in parallel. In addition, the stimulus driver element is 611 with electrodes 612 (Gold or platinum-iridium alloy) coupled, creating the stimulus driver element 611 is electrically connected to nerve conduction tissue (axons).

It should be appreciated that in certain embodiments immediately after the rectifier element 606 a voltage boosting device (not shown) may be inserted to provide the supply voltage available for stimulation and for operation of the integrated electronics, through the miniaturized LC "parallel" resonant circuit (ie, the coil device 601 and the capacitor device 607 ) to increase limits. This voltage booster circuit can enable electro-stimulation and other microtransponder operations using the smallest possible LC devices that can generate too low a voltage (<0.5V). Examples of high efficiency booster circuits include charge pumps and switch booster circuits using low threshold Schottky diodes. However, any suitable type of conventional high-efficiency voltage boosting circuit can of course be used in this capacity as long as it can produce the voltage required for the particular application to which the micro-transponder is applied.

As in 7 shown, the (in 6 external sync trigger circuit configuration use a differential filtering technique to detect the tripping signal resulting from a sudden power interruption 701 consists of the slower drop in transponder power voltage 702 during the interruption. In particular, the circuit configuration (in 6 ) in the stimulus timer element 610 a separate capacitor (C _major ) 605 to adjust the stimulus duration using a monostable multivibrator. The stimulus strength can be controlled externally by the strength of the external RF power coil 602 generated RF power field can be controlled. As the RF power field is modulated, the timing and frequency of the stimuli from all microtransponders become below the RF power coil 602 externally synchronized.

Using the (in 6 external synchronization triggering circuit configuration shown), the degree of spatiotemporal control of complex stimulation patterns is essentially unrestricted. In certain embodiments, the circuit configuration of the external synchronization trigger circuit may be further modified to be configured to demodulate the unique identity code of each microtransponder. This essentially allows the independent control of each microtransponder via RF signals. This additional capability may provide a method to convey the spatio-temporal dynamics necessary to restore natural sensations to artificial limbs or to allow for new sensory modalities (eg, sensing infrared images, etc.).

8th provides several graphs that summarize the results of testing a wireless microtransponder (with a demodulator element for triggering an external interrupt) under various device settings and input conditions of external RF power in accordance with one embodiment. In the first graphic representation 801 The external RF power coil modulates the RF power field to a first Transmit trigger signal setting resulting in a stimulus frequency of 2 Hz. As previously discussed, the stimulus frequency is controlled by a trigger signal that is generated when the RF power coil modulates the RF power signal. As in the second graph 802 Thus, where the stimulus frequency is equal to 10 Hz, the stimulus frequency is directly related to the RF power field modulation frequency.

While the stimulus frequency is controlled by external RF power field modulation settings, the stimulus current peak amplitude becomes as in the third plot 803 is controlled by the RF power setting. That is, the stimulus current peak amplitude is directly related to the RF power setting. For example, an RF power setting of 1 mW produces a stimulus current peak amplitude of 0.2 mA, an RF power setting of 2 mW generates a stimulus current peak amplitude of 0.35 mA, and an RF power setting of 4 mW produces a stimulus current peak amplitude of 0.5 mA. Of course, these are just examples of how the RF power setting affects the stimulus current peak amplitude. In practice, the effects of RF power adjustment on stimulus current peak amplitude may be increased or decreased depending on the particular application (eg, depth of implantation, proximity to interfering body structures such as bone, etc.) and device settings.

9A FIG. 10 is an illustration of one use of a plurality of wireless microtransponders distributed throughout the subcutaneous vascular beds and nerve terminalis fields, in accordance with one embodiment. FIG. As shown, over the affected area are subcutaneously in a distributed pattern under the skin 904 a plurality of independent wireless microtransponders 908 implanted. In this embodiment, each microtransponder is in the vicinity and / or at an interface with a branch of the subcutaneous sensory nerves 901 positioned to provide electrostimulation for these nerves. In one embodiment, only synchronous microtransponders are used. In another embodiment, only asynchronous microtransponders are used. In yet another embodiment, a combination of synchronous and asynchronous microtransponders is employed.

After using the microtransponder can be done by positioning an RF power coil 902 An electrical stimulation is applied near the site where the microtransponders are implanted. The parameters for effective electrical stimulation may depend on several factors, including: the size of the nerve or nerve fiber being stimulated, the effective electrode / nerve interface contact, the conductivity of the tissue matrix, and the geometric configuration of the stimulating fields. While clinical and empirical studies have determined a general range of suitable electrical stimulation parameters for conventional electrode techniques, the parameters for microscale stimulation of widely distributed fields of sensory neural fields are likely to differ substantially both in terms of stimulation currents and subjective sensory experience achieved by this stimulation.

The parameters for effective repetitive pulse stimulation using conventional electrode techniques will usually range in amplitude up to about 10 V (or up to about 1 mA), which may take up to about 1 millisecond, for periods ranging from several seconds to several Minutes, up to about 100 pulses / s repeated, reports. In an exemplary embodiment, effective repetitive pulse stimulation with an amplitude of less than 100 μA can be achieved, with stimulation pulses lasting less than 100 μs.

9B FIG. 4 is an illustration of a use of wireless microtransponders to enable coupling with deep microtransponder implants, in accordance with one embodiment. FIG. As shown here, two simple electrical wires lead 903 from the subdermal / subcutaneous implanted outer transmission coil 907 to the deeper subcutaneous implanted inner transmission coil 903 microtransponder implanted near the field 908 , Threading the wires 903 through the interstices between the muscles and the skin includes minimally invasive routine procedures that are as simple as passing the wires through a hypodermic tube similar to routine endoscopic procedures involving catheters. The minimal risks of such interstitial wires 903 are widely accepted.

The deep inner transmission coil 905 is implanted to work with the deeply implanted field of microtransponders 908 As needed, for treating a variety of clinical applications, it is located near deep targets of microstimulation such as deep peripheral nerves, muscles or organs such as the bladder or stomach. The inner transmission coil 905 is tuned for maximum coupling efficiency so that the resonance of the external coil 909 to the immediate vicinity of the implanted microtransponder 908 is extended. In addition to expanding the effective range of the microtransponder 908 Implants represents the inner transmission coil 905 another wireless Link that can maintain the integrity of any further protection barrier around the target site. For example, the inner transmission coil 905 microtransponders 908 which are embedded within a peripheral nerve without damaging the epineurium that protects the delicate tissue in a nerve. For optimal tuning of the transmission coils (eg the outer transmission coil 907 and the inner transmission coil 905 ) to the outer transmission coil 907 a variable capacitor or other tuning elements in a resonant tuning circuit 911 added where they can be implanted with minimal risk of tissue damage. In certain embodiments, this resonant tuning circuit is 911 necessary while in others it is unnecessary.

9C FIG. 4 is an illustration of a use of wireless microtransponders to enable coupling with deep nerve microtransponder implants, in accordance with one embodiment. FIG. As shown here, is an extraneural inner transmission coil 905 that are near (or interfere with) a nerve fiber or a cell cluster 901 is positioned over a simple pair of leads 903 that receives all the signals and power needed to operate the microtransponder implanted somewhere in the body 908 necessary over the directly effective area of any external coil 909 (eg, epidermis coil, etc.), with an outer transmission coil 907 connected. In certain embodiments, the subdermal outer transmission coil becomes 907 for maximum wireless near field magnetic coupling to the external coil 909 tuned and immediately under the external coil 909 just below the surface of the skin 904 implanted. This allows without long-term damage to the skin 904 and the risk of infection that is caused by the external coil 909 generated RF waves penetrate into the body. In other embodiments, the outer transmission coil 907 on the external coil 909 tuned and subcutaneously implanted deeper into the tissue. In some embodiments, between the inner transmission coil 905 and the outer transmission coil 907 a resonance tuning circuit 911 lie to the frequency of the signal at the inner transmission coil 905 while it is unnecessary in others.

10 FIG. 4 is an illustration of how wireless microtransponders may be implanted using a beveled rectangular hypodermic needle in accordance with one embodiment. As shown, the needle is 1002 curved in such a way that it is adapted (concavely sloped) to the transverse cervical curvature and guided without further dissection across the subcutaneous space above the base of the affected peripheral nervous tissue. When the surgeon becomes familiar with the technique, rapid introduction usually eliminates the need for even brief general anesthesia. After the placement of the microtransponder 1003 from the needle 1002 becomes the needle 1002 carefully retracted and the electrode placement and configuration can be evaluated using intraoperative testing. Using a temporary RF transmitter placed near the location where the microtransponder 1003 can be implanted, an electrical stimulation can be created so that the patient can report on the stimulation site, the stimulation intensity and the overall sensation.

10A FIG. 4 is an illustration of how an associated array of wireless microtransponders may be implanted using a beveled rectangular hypodermic needle in accordance with one embodiment. As in 10 shown is the needle 1002 curved in such a way that it is adapted (concavely sloped) to the transverse cervical curvature and without further dissection across the base of the affected nervous tissue with rapid insertion, which usually eliminates the need for any anesthesia, into the subcutaneous space above the base of the affected peripheral nerve tissue to be led. The microtransponder 1003 are connected together to form a connected arrangement 1008 to build.

11 13 is an illustration of a manufacturing sequence for helical type wireless microtransponders in accordance with one embodiment. In step 1102 is (a material on Pyrex ^® -based, but other materials may also be commonly used, so long as they are compatible with the one used for the spiral coil conductive material and the particular application to which the resulting micro-transponder is applied) on a substrate a layer of a gold spiral coil galvanically coated. As the conductor material, electroplated gold is used because of its high conductivity, oxidation resistance and proven ability to be implanted in biological tissue for long periods of time. However, it should be appreciated that other conductive materials may also be used as long as the material exhibits the conductivity and oxidation resistance properties required by the particular application to which the micro-transponders are applied. Typically, the gold spiral coil conductors have a thickness between approximately 5 μm to approximately 25 μm.

In one embodiment, the gold spiral coil assumes a first configuration in which the Gold conductor is approximately 10 microns wide and in which there is a distance of approximately 10 microns between the windings. In another embodiment, the gold spiral coil assumes a second configuration in which the gold conductor is approximately 20 μm wide and in which there is a spacing of approximately 20 μm between the windings. However, as will be appreciated by one of ordinary skill in the art, the scope of the present invention is not limited only to these exemplary gold spiral coil configurations, but rather includes any combination of conductor widths and pitch that is appropriate for the particular application to which the coil is applied.

In step 1104 The first layer of photoresist and the seed layer are removed. In one embodiment, the photoresist layer is removed using a conventional liquid resist stripper to chemically alter the photoresist so that it no longer adheres to the substrate. In another embodiment, the photoresist is removed using a plasma ashing process.

In step 1106 For example, a release layer of SU-8 photoresist is spin-coated and patterned to completely cover each spiral conductor. Usually, the SU-8 layer has a thickness of approximately 30 μm. In step 1108 For example, an uppermost seed layer is deposited on the SU-8 release layer using a conventional vapor deposition (PVD) process such as sputtering. In step 1110 For example, a top layer of a positive photoresist coating is patterned on the topmost seed layer and on the SU-8 release layer and in step 1112 A layer of platinum is applied using a conventional plating process. In step 1114 A chip capacitor and an RFID chip are attached to the conductive platinum layer using epoxy, and the electrical connections are made by wire bonding. In certain embodiments, the capacitor has a capacitance rating of up to 10,000 picofarads (pF).

It is possible to implant such small microtransponders simply by injecting them into the subdermal tissue. The patient may be positioned laterally or on the abdomen using local anesthesia at the injection site, depending on the incision entry point. The subdermal tissues immediately to the side of the incision are sharply undermined to accommodate a loop of the electrode created after placement and after tunneling to prevent electrode migration. A Tuohy needle is gently curved to conform to the posterior cervical curvature (concavely sloped) and is passed across the base of the affected peripheral nerves without further dissection across the subcutaneous space. When the surgeon masters the technique effortlessly, rapid needle insertion usually eliminates the need for even short-acting general anesthesia. After placing the electrode in the Tuohy needle, the needle is withdrawn and the electrode placement and configuration evaluated using intraoperative testing.

Following lead placement, a stimulation is applied to a different selected electrode combination using a temporary RF transmitter, which allows the patient on the operating table to report the location of the stimulation, the intensity of the stimulation, and the overall sensation. Based on previous experience with wired transponders, most patients should report immediate stimulation in the selected peripheral nerve distribution at voltage settings of 1 to 4 volts with medium pulse widths and frequencies. A report of burning pain or muscle pulling should warn the surgeon that the electrode has probably been placed either too close to the fascia or intramuscularly.

An exemplary microtransponder arrangement is preferably an array of connected microtransponders. The bonded assembly is made of or coated with a biocompatible material that is sufficiently strong to hold the microtransponders and remains intact during surgical explantation. An advantage of the joined arrangement is that removal of the assembly is simpler than unconnected microtransponders, which would be more difficult to position and extract individually from in the integrated mass of adhered tissues. Because the assembly may include a bonded assembly of any type of implanted medical device, the concept is flexible. The monolithic structure can hold the implanted devices together during explantation.

The bonded assembly can be made of several types of biocompatible materials. Exemplary synthetic materials suitable for the removable assembly include silicone elastomers or silicone hydrogels and plastics such as SU-8 or Parylene-C. Removable assemblies can also be constructed using biodegradable, long life polymers including natural materials such as polymers such as gelatin, silk or collagen based on protein, and polysaccharides such as cellulose or sugar based agarose. Other suitable biodegradable polymers including polyglycolic acids (PGA) polylactic acids (PLA) have been developed specifically for implant design. These construction materials provide a range of strength, durability and tissue adhesion properties suitable for a variety of specific implant applications. In addition, the surface of any array material may be coated by coating the implant with a variety of materials that are used extensively for this purpose, including formulations of PEG (polyethylene glycol) such as PEG-PLA and commercial products such as Greatbatch Biomimetic Coating (US Pat. U.S. Patent 6,759,338 B1 ) and Medtronics' trillium biosurface to enhance specific biological properties such as cell / protein adhesion and tissue responses.

The biocompatibility of the arrangement is very important. The bonded assembly may include a coating in the form of a monolayer or a thin layer of a biocompatible material. The benefits of coatings include the ability to associate proteins with the coating. The linked proteins can limit which cell types can adhere to the array. The coating can prevent protein adsorption and does not significantly increase the size of the device.

Porous 3D materials are designed to promote cell ingrowth and cell organization. The porous 3D material can act as a buffer between the tissue and the microtransponders to prevent reaction micro-movement. The potential benefits to implant / tissue integration must be balanced against the additional risks associated with increasing the overall size of the implant when adding these 3D materials.

The visibility of the implant can be improved by the addition of light colorants to the construction materials, thereby facilitating the visual location of the assembly within the surrounding tissue if it needs to be removed. This may include a marker dye that is globally integrated on or into the device. A preferred embodiment utilizes a fluorescent dye that becomes visible when exposed to suitable light sources because it offers the benefit of maximum luminescence at such a level that the implants can be seen through the skin.

12A shows a perspective view of the basic embodiment of an arrangement. The connected arrangement 1215 includes a pre-made strip where each microtransponder 1220 using SU-8 to obtain the association with adjacent microtransponders 1210 connected is. 12B shows a side view of the basic embodiment of an arrangement. The order 1215 consists of SU-8 and associated micro-transponders 1210 , 12C shows a plan view of the basic embodiment of an arrangement. An advantage of this design is that it does not require any additional materials or steps to make the mated assembly, making it relatively easy to manufacture.

13A shows a perspective view of an arrangement comprising exposed through windows in the array electrodes. The connected arrangement 1215 includes a solid strip, which is an interconnected array of individual microtransponders 1210 contains, each microtransponder 1210 with adjacent microtransponders 1210 connected is. In this embodiment, the top and bottom electrodes are through windows 1310 in the microtransponders 1210 free. 13B shows a side view of an arrangement 1215 passing through windows 1310 in the arrangement 1215 comprising exposed electrodes. 13C shows a plan view of an arrangement through windows 1310 in the arrangement 1215 comprising exposed electrodes. This embodiment may use a more durable material than SU-8, with better protection of the bonded and embedded microtransponders. In addition, the assembly may be more flexible than a prefabricated solid SU-8 assembly.

14A shows a perspective view of an arrangement comprising an ion-permeable strip. The ion permeable connected arrangement 1415 lies on surrounding tissue and the connected individual microtransponders 1210 are completely within the arrangement 1415 embedded. 14B shows a side view of an ion-permeable device. The microtransponder 1210 are completely within the ion permeable arrangement 1415 embedded. 14C shows a plan view of an arrangement comprising an ion-permeable strip. The embodiment may use a more durable material than SU-8, with the embedded microtransponder 1210 are better protected. In addition, the arrangement 1415 be more flexible than a prefabricated solid SU-8 assembly. The electrodes may be completely isolated from proteins and tissues, but still affect ions in solution. Since tissue would be kept a minimum distance away from the electrodes, there may be reduced efficiency.

15A shows a perspective view of the basic embodiment of a slotted arrangement. This type of arrangement is intended for permanent implantation and contains one in the surface or completely through sites along the Arrangement or in the micro transponder itself lowered slot, which is intended for tissue ingrowth, to ensure that the arrangement is in their place. The connected slotted arrangement 1215 includes a pre-made strip where each microtransponder 1210 using SU-8 to obtain the association with adjacent microtransponders 1210 connected is. Sections of the device surface such as directly over the microtransponders 1210 may be coated with a material to prevent protein adsorption. The slots 1505 through the arrangement 1215 between the microtransponders should accommodate tissue ingrowths to the arrangement 1215 permanently anchored in its place. 15B shows a side view of the basic embodiment of a slotted arrangement. The order 1215 includes SU-8 and associated micro-transponders 1210 with slits 1505 by the arrangement 1215 walk. 15C shows a plan view of the basic embodiment of a slotted arrangement.

16A has a perspective view of the basic version of an arrangement which is surrounded by a shell matrix. The connected arrangement 1215 includes a pre-made strip where each microtransponder 1210 using SU-8 to obtain the association with adjacent microtransponders 1210 connected is. A matrix 1605 made of biocompatible material surrounds the connected assembly 1215 to the connected arrangement 1215 completely surrounded. 16B shows a side view of the basic embodiment of an arrangement which is surrounded by a shell matrix. The biocompatible matrix 1605 closes the connected arrangement 1215 connected microtransponder 1210 one. 12C shows a plan view of the basic embodiment of an encircled by an envelope matrix arrangement. An advantage of this design is that there are no additional materials or steps for the preparation of the associated matrix 1215 are required, which relatively facilitates the manufacture and inclusion in the matrix.

The bonded matrix may also be formed of a biodegradable material. As the material of the bonded assembly is released, the micro-transponders are released to move freely and minimize tissue reactions. The most common examples of biodegradable materials include natural polymers based on proteins (eg, gelatin, collagen, silk) and polysaccharides (sugar-based polymers such as cellulose and starch) in various formulations (ie, proteo-saccharides such as agarose) containing a provide wide range of strength and degradation times. Other known acceptable biodegradable materials include polyglycolic acid (PGA) and polylactic acid (PLA).

Of course, the innovations of the present application are not limited to the disclosed embodiments, but may include various materials, configurations, locations, or other variations beyond the illustrated embodiments, which are exemplary only.

In accordance with various embodiments, there is provided a microtransponder assembly comprising: an assembly consisting of adjacent and physically connected wireless microtransponders; each microtransponder having a wireless interface.

In accordance with various embodiments, there is provided an implantable device comprising: an array of physically coupled embedded microtransponders having wireless interfaces; wherein the electrode surfaces on the array are exposed through windows in the individual microtransponders.

In accordance with various embodiments, there is provided a method of forming an implantable wireless electronic device, the method comprising the steps of: creating a removable array of embedded adjacent electronic devices on a single substrate; and powering the device using a wireless interface.

In accordance with various embodiments, there is provided a method of implanting wireless electronics into living tissue, the method comprising: implanting an array of physically connected and wirelessly powered electronic devices into tissue; and if the removal of the electronic devices is necessary, then exposing the assembly of connected electronic devices, and then removing the array of electronic devices from the living tissue.

In accordance with various embodiments, there is provided an electronic device for implantation, the device comprising: an array of physically connected embedded wireless devices; the assembly being internally permeable and resistant to ingrowth of non-conductive fibrous matter.

In accordance with various embodiments, there is provided a method of removing an implanted plurality of electronic devices, the method comprising the steps of: implanting the array with a surrounding matrix; Removing the tissue growth at a minimum distance from at least a portion of the connected electronic devices; Locating the device using an integrated tag; and surgically exposing the capture and release device.

In accordance with various embodiments, there is provided: a biocompatible electronic module implantable in living tissue, the module comprising: a plurality of electronic devices that are powered wirelessly and coupled together to one size a physically connected assembly form, which allows the implantation of a needle; and at least one electrical conduction path through the assembly connecting at least one port of the device to the surrounding tissue.

Modifications and changes

As those skilled in the art will appreciate, the innovative concepts described herein may be modified and changed over a wide range of applications, so that the scope of the patented subject matter is not limited to any of the specific example teachings given.

For example, in one embodiment, the joined microtransponders may be connected rather than an elongated or linear strip both longitudinally and transversely to form a geometric shape. The shapes may include squares, hexagons, rectangles, ovals, and circles.

In addition, the assembly may be formed on a single substrate with a chain or group of assemblies temporarily constructed to form a single integrated structure. In addition, it may be possible to construct connected assemblies using a monofilament line as a cord of microtransponders.

The specific implementations provided herein are not intended to limit the practice of the present innovations.

The following applications may contain additional information and alternative modifications: Attorney Docket No. MTSP-29P, Serial No. 61 / 088,099, filed 8/12/2008 and entitled "In Vivo Tests of Switched-Capacitor Neural Stimulation for Use in Minimally Invasive Wireless Implants; Attorney Docket No. MTSP-30P, Serial No. 61 / 088,774, filed Aug. 15, 2008 and entitled "Micro-Coils to Remotely Power Minimally Invasive Microtransponders in Deep Subcutaneous Applications"; Attorney docket No. MTSP-31P, Serial No. 61 / 079,905, filed 8/8/2008 and entitled "Microtransponders with Identified Reply for Subcutaneous Applications"; Attorney's Docket No. MTSP-33P, Serial No. 61 / 089,179, filed Aug. 15, 2008 and entitled "Addressable Micro-Transponders for Subcutaneous Applications"; Attorney's Docket No. MTSP-36P, Serial No. 61 / 079,004, filed 8/8/2008 and entitled "Microtransponder Array with Biocompatible Scaffold"; Attorney docket No. MTSP-38P, Serial No. 61 / 083,290, filed 24.7.2008 and entitled "Minimally Invasive Microtransponders for Subcutaneous Applications"; Attorney's Docket No. MTSP-39P, Serial No. 61 / 086,116, filed 4/8/2008 and entitled "Tintinnitus Treatment Methods and Apparatus"; Attorney Docket No. MTSP-40P, Serial No. 61 / 086,309, filed on Aug. 5, 2008 and entitled "Wireless Neurostimulators for Refractory Chronic Pain"; Attorney's Docket No. MTSP-41P, Serial No. 61 / 086,314, filed on Aug. 5, 2008 and entitled "Use of Wireless Microstimulators for Orofacial Pain"; Attorney Docket No. MTSP-42P, Serial No. 61 / 090,408, filed August 20, 2008 and entitled "Update: In Vivo Tests of Switched-Capacitor Neural Stimulation for Use in Minimally-Invasive Wireless Implants"; Attorney docket No. MTSP-43P, Serial No. 61 / 091,908, filed on Aug. 26, 2008 and entitled "Update: Minimally Invasive Microtransponders for Subcutaneous Applications"; Attorney Docket No. MTSP-44P, Serial No. 61 / 094,086 filed on 4/9/2008 and entitled "Microtransponder MicroStim System and Method"; Attorney docket No. MTSP-30, Serial No. ..., filed on ... and entitled "Transfer Coil Architecture"; Attorney's Dossier No. MTSP-31, Serial No. ..., filed on ... and entitled "Implantable Driver with Charge Balancing"; Attorney's Docket No. MTSP-32, Serial No. ..., filed on ... and entitled "A Biodelivery System for Microtransponder Array"; Attorney docket No. MTSP-46, Serial No. ..., filed on ... and entitled "Implanted Driver with Resistive Charge Balancing"; Attorney's Docket No. MTSP-28, Serial No. ..., filed on ... and entitled "Implantable Transponder Systems and Methods"; and Attorney Docket No. MTSP-48, Serial No. ..., filed on ... and entitled "Implantable Transponder Pulse Stimulation Systems and Methods", all of which are incorporated herein by reference.

Nothing in the description in the present application should be read to mean that any particular element, step, or function is an essential element that must be included in the scope of the claim: DER SCOPE OF THE PATENTED SUBJECT IS ONLY DEFINED BY THE PERMISSIBLE CLAIMS. In addition, none of these claims are intended to refer to paragraph six of the 35 USC, Section 112, unless the actual words "means to" are followed by a participle.

The claims as filed should be as comprehensive as possible and NO object has been intentionally abandoned, dedicated or dropped.

Summary

Arrangement of wireless micro-transponders constructed from a single structure of connected micro-transponders. The microtransponders may be configured as a linear array strip with interconnect material therebetween. The microtransponders may also be completely embedded within a strip of material or joined by a single, common substrate structure.

QUOTES INCLUDE IN THE DESCRIPTION

This list of the documents listed by the applicant has been generated automatically and is included solely for the better information of the reader. The list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions.

Cited patent literature

• US20020198572 [0007]
• US 20030212440 [0008]
• US 20030212440 [0009]
• US 20050137652 [0010]
• us 20060206162 [0011]
• US Pat. No. 6,759,338 B1 [0100]

Claims (73)

A microtransponder arrangement comprising: an array consisting of adjacent and physically connected wireless microtransponders; each microtransponder having a wireless interface. Arrangement according to claim 1, wherein the arrangement is an elongate strip. The assembly of claim 1, wherein the assembly includes both longitudinally and transversely connected wireless micro-transponders. Arrangement according to claim 3, wherein the connected wireless microtransponder form a geometric shape. The assembly of claim 1, wherein the connected wireless microtransponders form a geometric shape that may include at least one of the following: an elongated strip; a square; a rectangle; a hexagon; a circle; and an oval. Arrangement according to claim 1, wherein the arrangement comprises a material which is selected from the following group: Silicone elastomers; Silicone hydrogels; Plastic. The assembly of claim 6, wherein the plastic comprises a material selected from the group consisting of: SU-8; and Parylene-C. The assembly of claim 1, wherein the assembly is biodegradable and comprises a material selected from the group consisting of: Polymers based on protein; Sugar-based polysaccharides; Polyglycolic acids (PGA); and Polylactic acids (PLA). An assembly according to claim 8, wherein the protein-based polymers comprise a material selected from the group consisting of: Gelatin; Silk; and Collagen. An assembly according to claim 8, wherein the sugar-based polysaccharides comprise a material selected from the group consisting of: Cellulose; and Agarose. The assembly of claim 1, wherein the assembly is coated with a material comprising a material selected from the group consisting of: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The assembly of claim 1, further comprising: a solid material that contains fully embedded wireless microtransponders. Arrangement according to claim 1, in which the wireless microtransponder expose windows above and below lying electrodes. The assembly of claim 1, further comprising: an ion-permeable material that resists ingrowth of surrounding tissue; and connected wireless micro-transponders fully embedded therein. The assembly of claim 1, wherein the assembly comprises a single substrate. The assembly of claim 1, wherein the assembly includes a monofilament interconnecting the wireless microtransponders. The assembly of claim 1, wherein the assembly is implanted using a needle having a rectangular cross-section. Arrangement according to claim 17, wherein the needle is chamfered and curved. The assembly of claim 1, wherein the assembly includes tissue ingrowth slots. The assembly of claim 1, further comprising a matrix of biocompatible material that wraps the connected microtransponder assembly. The assembly of claim 1, wherein the assembly comprises a biodegradable material. An implantable device comprising: an array of physically connected embedded microtransponders having wireless interfaces; wherein the electrode surfaces on the array are exposed through windows in the individual microtransponders. The apparatus of claim 22, wherein the assembly comprises a material selected from the group consisting of: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The apparatus of claim 22, wherein the assembly comprises a material selected from the group consisting of: Silicone elastomers; Silicone hydrogels; Plastic. The device of claim 22, wherein the assembly is implanted using a beveled needle having a rectangular cross-section. Apparatus as claimed in claim 22, wherein the array removal can be accomplished by detecting and retracting the array from the surrounding tissue. The device of claim 22, wherein the assembly includes a common substrate. The device of claim 22, wherein the assembly includes tissue ingrowth slots for anchoring the assembly. Apparatus according to claim 22, wherein the array is surrounded by a matrix. The assembly of claim 22, wherein the assembly comprises a biodegradable material. A method of forming an implantable wireless electronic device, the method comprising the steps of: Creating a removable array of embedded adjacent electronic devices on a single substrate; and Powering the device using a wireless interface. The method of claim 31, wherein the assembly comprises a strip. The method of claim 31, wherein the assembly comprises a material selected from the group consisting of: Silicone elastomers; Silicone hydrogels; and Plastic. The method of claim 31, further comprising the step of: Coating the assembly with a material selected from the following group: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The method of claim 31, further comprising the steps of: Making the arrangement; and Position the assembly using the marker. The method of claim 31, wherein the embedded assembly on the individual microtransponders has electrode surfaces exposed through windows. The method of claim 31, wherein the embedded array is surrounded by a matrix. A method of implanting wireless electronics into living tissue, the method comprising: Implanting an array of physically connected and wirelessly powered electronic devices into tissue; and if removal of the electronic devices is necessary, then exposing the array of connected electronic devices and then removing the array of electronic devices from the living tissue. The method of claim 38, wherein the assembly is implanted by a needle that is further bevelled and curved and may include a Tuohy needle. The method of claim 38, further comprising the step of: Coating the assembly of electronic devices with a material selected from the following group: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The assembly of claim 40, wherein the connected electronic devices form a geometric shape that may include at least one of the following: an elongated strip; a square; a rectangle; a hexagon; a circle; and an oval. The method of claim 38, wherein the array of electronic devices includes an ion permeable material. The method of claim 38, wherein the assembly includes a common substrate for the electronic devices. The method of claim 38, wherein the assembly includes a monofilament interconnecting the electronic devices. The method of claim 38, wherein the arrangement is marked to facilitate locating for removal. The method of claim 38, further comprising the step of: surrounding the assembly with a biocompatible matrix. An electronic device for implantation, the device comprising: an array of physically connected embedded wireless devices; the assembly being internally permeable and resistant to ingrowth of non-conductive fibrous matter. An electronic device according to claim 47, wherein the device is marked. The electronic device of claim 48, wherein the label may include a fluorescent dye marker visible under suitable light sources through the skin. The method of claim 47, wherein the assembly includes both longitudinally and transversely connected wireless devices. The method of claim 47, wherein the array of co-embedded devices is removable and coated with a material selected from the group consisting of: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The assembly of claim 47, wherein the assembly comprises a biodegradable material. A method of removing an implanted plurality of electronic devices, the method comprising the steps of: Implanting the assembly with a surrounding matrix; Removing the tissue growth at a minimum distance from at least a portion of the connected electronic devices; Locating the device using an integrated tag; and Surgical exposure of the device for grasping and pulling free. The method of claim 53, wherein the prefabricated assembly comprises a geometric shape that may include at least one of the following: an elongated strip; a square; a rectangle; a hexagon; a circle; and an oval. The method of claim 53, wherein the prefabricated assembly can be ejected from a rectangular curved needle to the correct location. The method of claim 53, wherein the assembly of connected microelectronic devices is coated with a material selected from the group consisting of: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The method of claim 53, wherein the assembly comprises a material selected from the group consisting of: Silicone elastomers; Silicone hydrogels; and Plastic. The method of claim 53, wherein the assembly comprises a common substrate for the microelectronic devices. The assembly of claim 53, wherein the assembly comprises an ion permeable material that resists ingrowth of surrounding tissue. The device of claim 59, wherein the device comprises microelectronic devices embedded completely therein. The assembly of claim 53, further comprising: a sliding material coating confined to the surface of the electrodes on the microelectronic devices. The assembly of claim 53, wherein the assembly includes a monofilament linking the microelectronic devices. A biocompatible electronic module implantable in living tissue, the module comprising: a plurality of electronic devices that are powered wirelessly and coupled together to form a physically connected assembly of a size that permits implantation from a needle ; and at least one electrical conduction path through the assembly connecting at least one port of the device to the surrounding tissue. The biocompatible electronic module of claim 63, wherein the assembly includes both longitudinally and transversely connected electronic devices. The biocompatible electronic module of claim 63, wherein the assembly is physically connected using a material selected from the group consisting of: Silicone elastomers; Silicone hydrogels; Plastic; and Monofilament. The biocompatible electronic module of claim 63, wherein the electronic device is coated with a material comprising a material selected from the group consisting of: Polyethylene glycol (PEG); Polylactic acids (PLA); biomimetic coating; and Trillium Biooberfläche. The biocompatible electronic device of claim 63, wherein said device removal can be accomplished by manually capturing and retracting the device from surrounding tissue. The biocompatible electronic module of claim 63, wherein the electronic devices comprise a strip of material containing an embedded array of microtransponders. The biocompatible electronic module of claim 63, wherein the assembly comprises an ion-permeable strip that resists ingrowth of surrounding tissue and associated microtransponders fully embedded therein. The biocompatible electronic module of claim 63, wherein the assembly holds tissue at a minimum distance from at least a portion of the electronic device. The biocompatible electronic module of claim 63, wherein the electronic device includes a single substrate structure. A biocompatible electronic module according to claim 63, wherein the needle is curved and has a rectangular cross-section. The biocompatible electronic module of claim 63, wherein the assembly comprises a biodegradable material.

Images