WO2010107926A1 - Ensemble conduit blindé contre les interférences électromagnétiques pour dispositif médical implantable actif (aimd) - Google Patents

Ensemble conduit blindé contre les interférences électromagnétiques pour dispositif médical implantable actif (aimd) Download PDF

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Publication number
WO2010107926A1
WO2010107926A1 PCT/US2010/027677 US2010027677W WO2010107926A1 WO 2010107926 A1 WO2010107926 A1 WO 2010107926A1 US 2010027677 W US2010027677 W US 2010027677W WO 2010107926 A1 WO2010107926 A1 WO 2010107926A1
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WO
WIPO (PCT)
Prior art keywords
emi
conduit assembly
aimd
para
shielded conduit
Prior art date
Application number
PCT/US2010/027677
Other languages
English (en)
Inventor
Buehl E. Truex
Robert A. Stevenson
Richard L. Brendel
Original Assignee
Greatbatch Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US12/407,402 external-priority patent/US8195295B2/en
Priority claimed from US12/489,921 external-priority patent/US7751903B2/en
Priority claimed from US12/686,272 external-priority patent/US8509913B2/en
Priority claimed from US12/686,137 external-priority patent/US8989870B2/en
Application filed by Greatbatch Ltd. filed Critical Greatbatch Ltd.
Priority to EP10754066A priority Critical patent/EP2408520A4/fr
Publication of WO2010107926A1 publication Critical patent/WO2010107926A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/37—Monitoring; Protecting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/37—Monitoring; Protecting
    • A61N1/3718—Monitoring of or protection against external electromagnetic fields or currents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/08—Arrangements or circuits for monitoring, protecting, controlling or indicating
    • A61N1/086—Magnetic resonance imaging [MRI] compatible leads
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/375—Constructional arrangements, e.g. casings
    • A61N1/3752—Details of casing-lead connections
    • A61N1/3754—Feedthroughs

Definitions

  • the present invention generally relates to active implantable medical devices (AIMDs). More particularly, the present invention relates to an EMI shielded conduit for leads extending from the hermetic feedthrough terminal of an active implantable medical device to a remote electronic circuit board, substrate or network located within the AIMD hermetically sealed and electromagnetically shielded housing.
  • AIMDs active implantable medical devices
  • Feedthrough hermetic terminals are generally well-known in the art for connecting electrical signals through the housing or case of an AIMD such as those illustrated in FIG. 1 .
  • a hermetic terminal 1 00 comprises one or more conductive terminal pins 1 02a-102d supported by an insulative structure for feedthrough passage from the exterior to the interior of an AIMD electromagnetic shield housing 104.
  • Many different insulator structures and related mounting methods are known in the art for use in AIMDs, wherein the insulative structure also provides a hermetic seal to prevent entry of body fluids into the housing of the AIMD.
  • feedthrough terminal pins are typically connected to one or more implanted leads 1 06 and 106' are routed from the outside or body fluid side of the AIMD electromagnetic shield housing 1 04 to cardiac tissues such as those located in a right atrium 1 08 or in a right ventricle 1 10.
  • implanted leads 106 undesirably act as an antenna and thus tend to collect stray electromagnetic interference (EMI) signals from the patient environment for conducted transmission into the interior of the AIMD electromagnetic shield housing 104.
  • EMI signals may interfere with the proper operation of AIMD electronic circuits.
  • the AIMD internal electronic circuits are located on a circuit board or substrate 1 1 2. Also shown is an RF telemetry pin 1 14.
  • the circuit board 1 1 2 and the telecommunications circuit board 1 16 can be combined into one overall substrate or they may be broken down into several different substrates located within the AIMD electromagnetic shield housing 104.
  • there is a ceramic feedthrough filter capacitor 1 1 8 which is typical of many prior art devices.
  • the hermetic terminal 100 has been combined directly with frequency selective components such as the ceramic feedthrough filter capacitor 1 1 8 or MLCC chip capacitors or the like (not shown), to decouple or divert interfering signals from the point of lead ingress to the shielded housing of the AIMD.
  • frequency selective components such as the ceramic feedthrough filter capacitor 1 1 8 or MLCC chip capacitors or the like (not shown)
  • Examples of mounting MLCC chip capacitors to the hermetic terminals of AIMDs are more thoroughly described in U.S. 5,650,759 and 5,896,267, the contents of which are incorporated herein by reference. It is very important to decouple these signals at their point of ingress to the electromagnetically shielded AIMD so that such stray signals do not re-radiate or couple to sensitive circuits inside the AIMD electromagnetic shield housing 1 02.
  • FIGURE 3 is an example of good practice in the mounting of a prior art broadband EMI filter 1 20 such as the ceramic feedthrough capacitor 1 1 8.
  • the broadband EMI filter 1 20 has been mounted directly to or adjacent to the hermetic terminal 1 00 at the point of ingress of an implanted lead 1 22.
  • a leadwire 1 24 routed inside the AIMD electromagnetic shield housing 1 04 are free of high frequency EMI signals. Accordingly, the leadwires 1 24 cannot reradiate or couple undesirably to internal circuit board 1 1 2 electronic components.
  • FIGURE 4 is an example of prior art poor practice. In this case, the onboard EMI filter components have been mounted on the internal circuit board 1 1 2 inside of the AIMD electromagnetic shield housing 1 04.
  • the AIMD electromagnetic shield housing 104 is typically made of titanium, stainless steel, or other suitable biocompatible material which creates an equipotential shield housing. Seams are uniformly laser welded so that there are no openings.
  • An alternative is use of a ceramic, plastic or composite housing with an electromagnetic shield coating disposed on either its interior and/or exterior surfaces.
  • the AIMD electromagnetic shield housing 104 may also be coated with nano materials that form an RF shield.
  • the AIMD electromagnetic shield housing 104 provides hermeticity to protect the sensitive electronic circuits from the intrusion of body fluids.
  • the AIMD electromagnetic shield housing 1 04 both reflects and absorbs incident electromagnetic waves.
  • the AIMD electromagnetic shield housing 104 also forms a very convenient equipotential surface to which high frequency EMI signals conducted from the implanted leads 1 22 may be decoupled/diverted. This is typically done using passive or active filter elements which can be mounted directly on or adjacent to the point of AIMD housing implanted lead 1 22 ingress. In the prior art, the optimal location is to place such bypass (lowpass) filters on or adjacent to the hermetic feedthrough pin terminal.
  • the ceramic feedthrough filter capacitors 1 1 8 are typically mounted on the hermetic terminal 1 00 and provide a low impedance at high frequencies from the leadwires 1 24 to the AIMD electromagnetic shield housing 1 04, thereby shorting or diverting high frequency EMI signals to the housing 1 04.
  • the high frequency EMI energy is diverted to the AIMD electromagnetic shield housing 104, it simply circulates as eddy currents resulting in a few milliwatts of insignificant power dissipation as a small amount of heat. This results in a miniscule and insignificant temperature rise of the AIMD electromagnetic shield housing 104.
  • FIGURE 5 is an illustration of the attempt by lntermedics to place an MLCC chip capacitor 1 28 on a flex cable 1 30 located within the AIMD electromagnetic shield housing 1 04.
  • the flex cable 1 30 was unshielded but could have a ground circuit trace 1 32. It also has an active circuit trace 1 34.
  • the MLCC chip capacitor 1 28 was located between a pair of electrical connections 1 36a, 1 36b between the ground circuit trace 1 32 and the active circuit trace 1 34.
  • lead which is synonymous with implanted lead, shall mean the lead or leads that are routed from the exterior of the AIMD electromagnetic shield housing 104 into body tissues.
  • leadwire refers to wiring, flex cables or circuit traces inside of the AIMD electromagnetic shield housing 104.
  • the term remote as applied to a circuit board, substrate, capacitor, low pass filter, L-C trap filter, electronic filter, bandstop filter, high voltage suppression array, diode array, and/or short to housing switch network shall mean that any combination of these circuits are mounted remotely relative to the AIMD hermetic seal at or near the distal end of the shielded conduit (usually mounted on an AIMD circuit board or substrate).
  • the novel shielded conduit will both shield the leadwires routed from the AIMD hermetic terminal to the circuit board, remote substrate, capacitor, low pass filter, L-C trap filter, electronic filter, bandstop filter, high voltage suppression array, diode array, and/or short to housing switch network and at the same time also provide a low impedance RF ground return to the overall AIMD electromagnetic shield housing 1 04 for said remote circuits.
  • EMI filtered feedthrough hermetic terminals are shown and described in U.S. 4,424,551 , U.S. 5,333,095, U.S. 5,905,627, U.S. 5,973,906, U.S. 5,959,829, and U.S.
  • hermetic terminal subassembly is typically manufactured with biocompatible materials including platinum, platinum iridium pins, gold brazes and the like. In other words, a significant amount of the cost of this subassembly is due to the precious metals involved in its design.
  • FIGURE 1 illustrates various types of active implantable and external medical devices 14Oa-I 4Oi that are currently in use.
  • FIG. 1 is a wire formed diagram of a generic human body showing a number of implanted medical devices.
  • Numeral 140a represents a family of hearing devices which can include the group of cochlear implants, piezoelectric sound bridge transducers and the like.
  • Numeral 1 40b represents a variety of neurostimulators and brain stimulators. Neurostimulators are used to stimulate the Vagus nerve, for example, to treat epilepsy, obesity and depression.
  • Brain stimulators are pacemaker-like devices and include electrodes implanted deep into the brain for sensing the onset of the seizure and also providing electrical stimulation to brain tissue to prevent a seizure from actually occurring.
  • the leadwires associated with a deep brain stimulator are often placed using real time MRI imaging. Most commonly such leadwires are placed during real time MRI.
  • Numeral 1 40c shows a cardiac pacemaker which is well-known in the art.
  • Numeral 14Od includes the family of left ventricular assist devices (LVAD's), and artificial hearts, including the recently introduced artificial heart known as the Abiocor.
  • Numeral 1 4Oe includes an entire family of drug pumps which can be used for dispensing of insulin, chemotherapy drugs, pain medications and the like.
  • Insulin pumps are evolving from passive devices to ones that have sensors and closed loop systems. That is, real time monitoring of blood sugar levels will occur. These devices tend to be more sensitive to EMI than passive pumps that have no sense circuitry or externally implanted leadwires.
  • Numeral 1 4Of includes a variety of bone growth stimulators for rapid healing of fractures.
  • Numeral 14Og includes urinary incontinence devices.
  • Numeral 1 4Oh includes the family of pain relief spinal cord stimulators and anti-tremor stimulators.
  • Numeral 14Oh also includes an entire family of other types of neurostimulators used to block pain.
  • Numeral 1 4Oi includes a family of implantable cardioverter defibrillator (ICD) devices and also includes the family of congestive heart failure devices (CHF). This is also known in the art as cardio resynchronization therapy devices, otherwise known as CRT devices.
  • ICD implantable cardioverter defibrillator
  • CHF congestive heart failure devices
  • FIGURE 6 is a prior art unipolar discoidal feedthrough capacitor 1 42, which has an active internal electrode plate set 144 and a ground electrode plate set 1 46. An inside diameter termination surface 1 48 is connected electrically to the active electrode plate set 1 44. An outside diameter termination surface 1 50 is both solderable and electrically conductive, and it is connected to the ground electrode plate set 146.
  • FIGURE 7 is a cross-section of the unipolar discoidal feedthrough capacitor 142 of FIG. 6 shown mounted to a feedthrough hermetic terminal 1 52 of an active implantable medical device (AIMD). In prior art discoidal feedthrough capacitor devices 142, the leadwire 1 24 is continuous.
  • AIMD active implantable medical device
  • the feedthrough hermetic terminal 1 52 is attached to, typically, a titanium housing 1 54, for example, of a cardiac pacemaker.
  • An insulator 1 56 like alumina ceramic or glass, is disposed within the ferrule 1 38 and forms a hermetic seal against body fluids.
  • the leadwire 1 24 extends through the feedthrough hermetic terminal 1 52, passing through aligned passageways through the insulator 1 56 and the unipolar discoidal feedthrough capacitor 1 42.
  • a gold braze 1 58 forms a hermetic seal joint between the leadwire 1 24 and the insulator 1 56.
  • a second gold braze 1 60 forms a hermetic seal joint between the alumina insulator 1 56 and the ferrule 1 38.
  • a laser weld 1 62 provides a hermetic seal joint between the ferrule 1 38 and the titanium housing 1 54.
  • the unipolar discoidal feedthrough capacitor 142 is shown surface mounted in accordance with U.S. 5,333,095, and has an electrical connection 1 64 between its inside diameter metallization 148 and hence the active electrode plate set 1 44 and the leadwire 1 24. There is also an outside diameter electrical connection 1 64 which connects to the outside diameter metallization 1 50 and hence the ground electrode plate set 1 46 to the ferrule 1 38.
  • Feedthrough capacitors are very efficient high frequency devices that have minimal series inductance. This allows them to operate as EMI filters over very broad frequency ranges.
  • FIG. 7 Another way to describe a prior art unipolar discoidal feedthrough capacitor 1 42 is as a three- terminal capacitor. Three-terminal devices generally act as transmission lines. One can see that there is a current 1 68 that passes into the leadwire 1 24. On the body fluid side there is generally an implanted lead 1 22 which can undesirably act as an antenna which can pick up energy from environmental emitters. This energy is known as electromagnetic interference (EMI). Cell phones, microwave ovens and the like have all been implicated in causing interference with active implantable medical devices. If this interference enters the leadwire 1 24 at a first terminal 1 70 (FIG.
  • EMI electromagnetic interference
  • the unipolar discoidal feedthrough capacitor 142 Upon exiting, the undesirable high frequency EMI has been cleaned off of the normal low frequency circuit current (such as pacemaker pacing pulses or biologic frequency sensors) so that the high frequency EMI has been significantly attenuated.
  • the high frequency energy passes from the first terminal 1 70 to a second terminal 1 72 (FIGS. 7 and 8), it is diverted through the unipolar discoidal feedthrough capacitor 1 42 to a ground terminal 1 74 which is also known as the third terminal or terminal 3.
  • the ground terminal 1 74 is the connection to the overall electromagnetically shielded housing of the AIMD.
  • the unipolar discoidal feedthrough capacitor 142 also performs two other important functions: (a) the internal active electrodes 1 44 and the internal ground electrodes 1 46 act as a continuous part of the overall electromagnetic shield housing of the electronic device or module which physically blocks direct entry of high frequency RF energy through the feedthrough hermetic terminal 1 52 or equivalent opening for leadwire ingress and egress in the otherwise completely shielded housing (such RF energy, if it does penetrate inside the shielded housing can couple to and interfere with sensitive electronic circuitry), and; (b) the unipolar discoidal feedthrough capacitor 142 very effectively shunts undesired high frequency EMI signals off of the leadwires 1 24 to the overall shield housing where such energy is dissipated in eddy currents resulting in a very small temperature rise.
  • FIGURE 8 is a schematic diagram showing the unipolar discoidal feedthrough capacitor 1 42 previously described in connection with FIGS. 6 and
  • FIGURE 9 is a quadpolar prior art feedthrough capacitor 1 76 which is similar in construction to that previously described in FIG. 6 except that it has four through holes.
  • FIGURE 1 0 is a cross-section showing the internal active electrodes
  • FIGURE 1 1 is a schematic diagram showing the four discrete feedthrough capacitors comprising the quadpolar feedthrough capacitor 1 76 of
  • FIGURE 1 2 is an exploded electrode view showing the inner and outer diameter electrodes of the unipolar discoidal feedthrough capacitor 142 of FIGS. 6 and 7. One can see the active electrode plates set 1 44 and the ground electrode plate set 1 46. A cover layer 1 78 is put on the top and bottom for added electrical installation and mechanical strength.
  • FIGURE 1 3 is an exploded view of the interior electrodes of the prior art quadpolar feedthrough capacitor 1 76 of FIG. 9. The active electrode plate sets are shown as 1 44 and the ground electrode plates are shown as 1 46. The cover layers 1 78 serve the same purpose as previously described in connection with FIG. 1 2.
  • FIGURE 1 4 is a prior art monolithic ceramic capacitor (MLCC) 1 80. These are made by the hundreds of millions per day to service consumer electronics and other markets. Virtually all computers, cell phones and other types of electronic devices have many of these.
  • the MLCC 1 80 has a body 1 82 generally consisting of a high dielectric constant ceramic such as barium titinate. It also has a pair of solderable termination surfaces 1 84, 1 84' at either end. These solderable termination surfaces 1 84, 1 84' provide a convenient way to make a connection to the internal electrode plates 1 44, 146 of the MLCC capacitor 1 80.
  • FIG. 1 4 can also take the shape and characteristics of a number of other types of capacitor technologies, including rectangular, cylindrical, round, tantalum, aluminum electrolytic, stacked film or any other type of capacitor technology.
  • FIGURE 1 5 is a sectional view taken from section 1 5-1 5 in FIG. 1 4.
  • the MCLL 1 80 includes a left hand electrode plate set 1 86 and a right hand electrode plate set 1 88.
  • the opposite, right hand electrode plate set 1 88 is shown connected to the external metallization surface 1 84'.
  • Prior art MLCC 1 80 and equivalent chip capacitors are also known as two-terminal capacitors. That is, there are only two ways electrical energy can connect to the body of the capacitor. In FIGS. 1 4 and 1 5, the first terminal 1 70 is on the left side and the second terminal 1 72 is on the right side.
  • FIGURE 1 6 is the schematic diagram of the MLCC chip capacitor 1 80 illustrated in FIGS. 1 4 and 1 5.
  • FIGURE 1 7 is a different type of prior art MLCC feedthrough capacitor 1 80 that is built into a special configuration known in the art by some as a flat-through capacitor 1 90.
  • the flat-through capacitor 1 90 exhibits ideal capacitance behavior versus frequency. That is, its attenuation curve versus frequency is nearly ideal. This is because it is truly a three-terminal device which acts as a transmission line in a manner similar to those of prior art unipolar discoidal feedthrough capacitors 1 42. This is better understood by referring to its internal electrode plate geometry as shown in FIGURE 1 8, wherein a through or active electrode plate 1 44 is sandwiched between two ground electrode plates 1 46, 1 46'.
  • the through or active electrode plate 1 44 is connected at both ends by termination surfaces 1 84 and 1 84'.
  • the flat-through capacitor 1 90 When the flat-through capacitor 1 90 is mounted between the circuit trace lands 1 92 and 1 92' as shown in FIG. 1 7, this connects the circuit trace together between points 1 92 and 1 92'. Referring to the active electrode plate 1 44 in FIG. 1 8, one can see the current 168 entering. If this is a high frequency EMI current, it will be attenuated along its length by the capacitance of the flat- through capacitor 1 90 and emerge as a much smaller in amplitude EMI signal at the second terminal 1 72 as 168'. Similar to the unipolar discoidal feedthrough capacitor 142, the flat-through capacitor 1 90 is also a three-terminal capacitor as illustrated in FIG.
  • Monolithic ceramic manufacturing limitations on electrode thickness and conductivity means that the prior art flat-through capacitors 1 90 have relatively high series resistance and can only be rated to a few hundred milliamps or a few amps at best (however, an implantable defibrillator must deliver a high voltage pulse of over 20-amps).
  • Prior art MLCC and flat-through electrodes must be kept relatively thin to promote ceramic grain growth through the electrodes in order to keep the capacitor layers from delaminating during manufacturing or worse yet, during subsequent mechanical or thermal shocks which can cause latent failures.
  • FIGURE 1 9 is a schematic diagram of the prior art flat-through capacitor 1 90 shown in FIG. 1 7. Note that this schematic diagram is the same as that for the unipolar discoidal feedthrough capacitor 1 42 shown in FIGS. 6 and 7. The difference is that the unipolar discoidal feedthrough capacitor 142 is inherently configured to be mounted as an integral part of an overall shield which precludes the problem of the RF coupling 1 94 (see FIGS. 9-1 1 ).
  • FIGURE 20 illustrates the attenuation versus frequency response curve which is shown generically for the flat-through capacitor 1 92 of FIG. 1 7. If it were not for cross-coupling of RF energy, it would perform as an ideal or nearly perfect capacitor.
  • the shield should extend all the way to the low pass filter elements such that no coupling or re-radiation inside of the device can occur.
  • An EMI shielded conduit assembly for an active implantable medical device includes an EMI shield housing for the AIMD, a hermetic feedthrough terminal associated with the AIMD housing, an electronic circuit board, substrate or network disposed within the AIMD housing remote from the hermetic feedthrough terminal, at least one leadwire extending from the hermetic feedthrough terminal to the remote electronic circuit board, substrate or network and an EMI shield conductively coupled to the AIMD housing and substantially co-extending about the leadwire in non-conductive relation thereto.
  • the EMI shielded conduit assembly may include a plurality of leadwires extending from the hermetic feedthrough terminal to the remote electronic circuit board, substrate or network.
  • a non-conductive insulator may be disposed between each leadwire and its respective EMI shield.
  • the EMI shield may include multiple EMI shields conductively coupled to the AIMD housing and each co-extensively extending about at least one respective leadwire in non-conductive relation thereto.
  • the electronic circuit board, substrate or network preferably includes a low pass EMI filter, an L-C trap, a bandstop filter, a programmable short-to-housing switch network, or a combination thereof.
  • the low pass EMI filter may include a capacitor, a feedthrough capacitor, an MLCC chip capacitor, a flat-through capacitor, an X2Y attenuator, a multi-element low-pass filter, an active electronic filter, or a combination thereof.
  • the low pass EMI filter and the L-C trap may be grounded to the EMI shield.
  • the low pass filter, the L-C trap, or the bandstop filter may be disposed on the circuit board or the substrate.
  • the EMI shielded conduit assembly may further include a high voltage suppression network associated with the remote electronic circuit board, substrate or network.
  • the high voltage suppression network is preferably grounded to the EMI shield.
  • the high voltage suppression network includes a diode array.
  • the EMI shield itself preferably includes a conductive heat-shrink tubing, a conductive foil, wire, braid, mesh, circuit trace, or solid tubular material.
  • the EMI shield is preferably radially spaced from the leadwires and may include a flex cable embodying at least one of the leadwires and the EMI shield.
  • the hermetic feedthrough terminal may include a ferrule conductively coupled to the AIMD housing.
  • the EMI shield is preferably conductively coupled to the ferrule.
  • the AIMD housing may further include a conductive equipotential surface, such as a metallic can.
  • FIGURE 1 is a wire-form diagram of a generic human body showing a number of exemplary active implantable medical devices (AIMD);
  • FIGURE 2 is an illustration of a human heart and a sample cardiac pacemaker having implantable leads implanted in the right atrium or right ventricular of the heart;
  • FIGURE 3 is a sectional view of an AIMD housing having the EMI filter mounted directly to the hermetic terminal at the point of ingress of the implantable leadwires;
  • FIGURE 4 is a sectional view similar to FIG. 3, of an AIMD housing having an onboard EMI filter on the internal circuit board such that EMI signals re-radiate from internal leadwires to the internal circuit board;
  • FIGURE 5 illustrates an MLCC chip capacitor on a flex cable located within the AIMD housing
  • FIGURE 6 is a fragmented perspective view of a prior art unipolar discoidal feedthrough capacitor
  • FIGURE 7 is a cross-sectional view of the feedthrough capacitor of
  • FIGURE 8 is an electrical schematic diagram of the feedthrough capacitor of FIGS. 6 and 7;
  • FIGURE 9 is a perspective view of a quadpolar feedthrough capacitor
  • FIGURE 1 0 is a cross-sectional view of the quadpolar feedthrough capacitor, taken along the line 10-10 of FIG. 9;
  • FIGURE 1 1 is an electrical schematic diagram of the quadpolar feedthrough capacitor of FIGS. 9 and 1 0;
  • FIGURE 1 2 is an exploded perspective view illustrating the electrode lay-ups of the unipolar feedthrough capacitor of FIGS. 6 and 7;
  • FIGURE 1 3 is an exploded perspective view illustrating the electrode lay-ups of the quadpolar feedthrough capacitor shown in FIGS. 9 and 10;
  • FIGURE 1 4 is a perspective view of a monolithic ceramic capacitor
  • FIGURE 1 5 is a cross-sectional view of the monolithic ceramic capacitor, taken along the line 1 5-1 5 of FIG. 1 4;
  • FIGURE 1 6 is an electrical schematic diagram of an ideal MLCC capacitor as illustrated in FIGS. 1 4 and 1 5;
  • FIGURE 1 7 is a perspective view of a prior art flat-through capacitor
  • FIGURE 1 8 illustrates the internal electrode array of the flat- through capacitor of FIG. 1 7;
  • FIGURE 1 9 is an electrical schematic drawing of the prior art flat- through capacitor of FIGS. 1 7 and 1 8;
  • FIGURE 20 is a graph illustrating the attenuation verses frequency response of the flat-through capacitor of FIGS. 1 7 and 1 8;
  • FIGURE 21 is a fragmented and partially sectional view of an EMI shielded conduit assembly for an AIMD, in accordance with the present invention.
  • FIGURE 22 is an end view of the EMI shielded conduit assembly taken generally from the line 22-22 of FIG. 21 ;
  • FIGURE 23 is an enlarged view of a circuit junction, taken of the area indicated by the reference number 23 in FIG. 21 ;
  • FIGURE 24 is an enlarged cross-sectional view of the circuit junction, taken along the line 24-24 of FIG. 23;
  • FIGURE 25 is a sectional view similar to FIG. 21 , except that the shielded conduit is replaced by a conductive heat-shrink tubing;
  • FIGURE 26 illustrates the heat-shrink tubing shrunk around four leadwires;
  • FIGURE 27 is an end sectional view taken generally along the line 27-27 of FIG. 26, illustrating the four leadwires within the shrunk heat-shrink tubing;
  • FIGURE 28 is an electrical schematic diagram of the EMI shielded conduit assembly shown in FIGS. 21 -27;
  • FIGURE 29 is a fragmented perspective view of a particular type of
  • EMI shield having a braid shielding
  • FIGURE 30 is an end view of an EMI shield having an insulation material disposed between the leadwire and the EMI shield conduit;
  • FIGURE 31 is an elevational view of the solid copper EMI shield conduit of FIG. 30;
  • FIGURE 32 is a fragmented perspective view of a coaxial wound wire forming an EMI shield conduit
  • FIGURE 33 is a perspective view of an alternative EMI shield conduit having a conductive foil wound around insulation material disposed around the leadwire;
  • FIGURE 34 is a perspective view similar to FIG. 33, further illustrating multiple leadwires disposed within the insulation material surrounded by the conductive foil;
  • FIGURE 35 is fragmented perspective view of an EMI shielded conduit formed from a shielded mesh interwoven with conductive strands;
  • FIGURE 36 is an enlarged view of the shielded mesh interwoven with the conductive strands, taken about the area designated by reference number 36 in FIG. 35;
  • FIGURE 37 is a fragmented perspective view of an EMI shield conduit mounted to a circuit board having multiple MLCC chip capacitors;
  • FIGURE 38 is an electrical schematic diagram of the remote MLCC mounted filter illustrated in FIG. 37;
  • FIGURE 39 is a perspective view of a multi-element chip capacitor monolithic array that may be used in place of the four separate MLCC capacitors shown in FIG. 37;
  • FIGURE 40 shows the internal active electrodes (AE) of the multielement chip capacitor monolithic array of FIG. 39;
  • FIGURE 41 illustrates an internal ground electrode (GE) of the multi-element chip capacitor monolithic array of FIG. 39;
  • FIGURE 42 is a circuit diagram illustrating an embodiment wherein the EMI shield conduit has no low pass filter;
  • FIGURE 43 is a circuit diagram illustrating a single element inductor low pass filter
  • FIGURE 44 is a circuit diagram illustrating an L section low pass filter including an inductor and a capacitor
  • FIGURE 45 is a circuit diagram illustrating a reverse low pass filter where the capacitor points toward the hermetic seal;
  • FIGURE 46 is a circuit diagram illustrating a T filter;
  • FIGURE 47 is a circuit diagram illustrating a Pl filter;
  • FIGURE 48 is a circuit diagram illustrating an n-element low pass filter;
  • FIGURE 49 is a circuit diagram illustrating a bandstop filter in series with a leadwire having an inductor and a capacitor in parallel;
  • FIGURE 50 is a circuit diagram illustrating an L-C trap filter;
  • FIGURE 51 is a circuit diagram illustrating the combination of a low pass filter, a bandstop filter and an L-C trap filter;
  • FIGURE 52 is a circuit diagram illustrating the combination of an L-
  • FIGURE 53 is a circuit diagram illustrating an automatic or programmable electronic short-to-housing switch network chip or electronic switch array
  • FIGURE 54 illustrates a prior art connection of a flex cable to leadwires that pass through hermetic terminal in non-conductive relationship
  • FIGURE 55 is a cross-sectional view of an improved flex cable embodying the present invention.
  • FIGURE 56 is a perspective view of the flex cable of FIG. 55 connected to a circuit board or substrate having a flat-through capacitor;
  • FIGURE 57 illustrates the lay-up of the active electrode plate set
  • FIGURE 58 illustrates the lay-up of the ground electrode plate (GEP) of the flat-through capacitor of FIG. 56;
  • FIGURE 59 is a sectional view taken along line 59-59 of FIG. 55;
  • FIGURE 60 is a sectional view taken along line 60-60 of FIG. 55, illustrating one of a pair of coaxially surrounding shields disposed about the circuit trace;
  • FIGURE 61 is a sectional view taken along the line 61 -61 of FIG. 55, illustrating an alternative to the internal circuit traces described with respect to FIG. 59;
  • FIGURE 62 illustrates the bottom shield ground of the flex cable of FIGS. 55 and 56;
  • FIGURE 63 is a cross-sectional view of the hermetic seal assembly taken along the line 63-63 of FIG. 55;
  • FIGURE 64 is a perspective view of an attachment cap used to connect a shielded flat-through EMI filter to various types of hermetic or non- hermetic seals;
  • FIGURE 65 is a cross-sectional view of a hermetic terminal including the cap of FIG. 64;
  • FIGURE 66 is a cross-sectional view illustrating a hermetic terminal assembly embodying the present invention.
  • FIGURE 67 is an enlarged perspective view of a cap assembly, taken generally of the area indicated by line 67-67 of FIG. 66;
  • FIGURE 68 is a perspective view of a cylindrical or coaxial shielded conduit attached to a stamped or machine metallic lid cover to shield an inline octa-polar assembly;
  • FIGURE 69 is a diagrammatic view of the full length of the EMI shielded conduit of FIG. 68;
  • FIGURE 70 is a partially exploded perspective view of a shield conduit and cover spaced from a feedthrough capacitor;
  • FIGURE 71 illustrates internal ground electrode plates (GEP) of the feedthrough capacitor of FIG. 70;
  • FIGURE 72 illustrates internal active electrode plates (AEP) of the feedthrough capacitor of FIG. 70;
  • FIGURE 73 is a perspective view illustrating a flat-through capacitor mounted to a shield plate designed to be soldered to a cover assembly;
  • FIGURE 74 illustrates the lay-up of the active electrode plates (AEP) of the flat-through capacitor of FIG. 73;
  • FIGURE 75 illustrates a ground electrode plate (GEP) of the flat- through capacitor of FIG. 73;
  • FIGURE 76 is a schematic illustrating an alternative embodiment of a flat-through capacitor electrically and mechanically connected directly to the inside of a surface of the cover assembly;
  • FIGURE 77 is an end view of the feedthrough capacitor, taken from the perspective of arrow 77 of FIG. 76;
  • FIGURE 78 illustrates the active electrode plates (AEP) of the flat- through capacitor of FIG. 76.
  • FIGURE 79 illustrates the ground electrode plate (GEP) of the flat- through capacitor of FIG. 76.
  • the EMI shielded conduit assembly for an active implantable medical device comprises: (1 ) an EMI shielded housing for the AIMD; (2) a hermetic feedthrough terminal associated with the AIMD housing; (3) an electronic circuit board, substrate or network disposed within the AIMD housing remote from the hermetic feedthrough terminal; (4) at least one leadwire extending from the hermetic feedthrough terminal to the remote electronic circuit board, substrate or network; and (5) an EMI shield conductively coupled to the AIMD housing and co-extensively extending about the at least one leadwire in non-conductive relation.
  • functionally equivalent components of various embodiments will be referred to by the same reference numbers or letters.
  • FIGURE 21 illustrates the basic components of an EMI shielded conduit assembly 1 96 for an active implantable medical device (AIMD) as outlined above.
  • the conductive ferrule 1 38 of a hermetic seal 1 98 is generally of titanium, platinum, or similar biocompatible metal.
  • the laser weld 1 62 hermetically seals the AIMD electromagnetic housing 1 04.
  • the hermetic seal 1 98 embodies a set of terminal pins 200a-200d attached to the implanted leads 1 22a-l 22d, which the terminal pins 200a-200d pass through in non- conductive relation.
  • a connector header block mounted outside the AIMD electromagnetic shield housing 104 in accordance with ISO standard IS-I or IS-4.
  • the hermetic seal 1 98 typically comprises an alumina ceramic or glass insulator (not shown). It is important that the metallic ferrule 1 38 be electrically a continuous part of the overall AIMD electromagnetic shield housing 1 04.
  • the novel EMI shielded conduit assembly 1 96 connects electrically to the ferrule 1 38 of the hermetic terminal seal 1 98. If there is no ferrule present, the EMI shielded conduit assembly 1 96 may be electrically connected directly to the AIMD electromagnetic shield housing 1 04. This conductive EMI shielded conduit assembly 1 96 extends down to an AIMD electronic circuit board, substrate or network 202. In a preferred embodiment, there are a set of conductive support tabs or feet 204 which are electrically connected to an EMI shield206.
  • the EMI shield 206 can be continuous solid (flexible) tubing, a shield braid, shielded wires, shielded foil, shielded mesh or even conductive circuit traces within a flex cable. It is important that this EMI shield 206 at least partially co-extensively surround the AIMD internal leadwires 1 24a-l 24d. This is because the implanted leads 1 22a-l 22d, for example, in the case of a cardiac pacemaker, are routed endocardially to cardiac chambers. These implanted leads 1 22a-l 22d can also undesirably act as antennas which can pick up stray and unwanted EMI.
  • a filter capacitor component 210 is shown as an integral part of the overall EMI shielded conduit assembly 1 96. As will be shown in subsequent drawings, it can be eliminated, it can be placed on the circuit board 202 or consist of alternate components.
  • the EMI filter in this case, is a quadpolar low pass filter consisting of the filter capacitor component 21 0. This is identical to the prior art quadpolar feedthrough capacitor 1 76 shown in FIGS. 9 - 1 1 and 1 3.
  • the conductive support feet 204 are electrically connected to the EMI shield 206 and are also connected to a set of ground circuit traces 21 2a-21 2b on the circuit board 202.
  • the implanted leads 1 24a-l 24d and the hermetic terminal pins 200a-200d are exposed to body fluids and have to be of suitable biocompatible materials, such as platinum, platinum-iridium, niobium, palladium and the like.
  • a circuit junction connection 214 is shown to make a connection from the hermetic seal terminal pin(s) 200a-200d to the much lower cost leadwires 1 24a-l 24d.
  • the circuit junction connections 21 4 can be a simple solder joint, a crimp or twist connector as illustrated, a plug-in pin, or any other method of joining two leadwires together.
  • FIGURE 23 is a blown-up view of the circuit junction connection 214 of FIG. 21 .
  • Shown is a novel crimp connection 216.
  • the crimp connection 216 has a crimp 21 8 to the hermetic terminal pin 200a and also includes a crimp 21 8' to the leadwire 1 24a.
  • An optional hole 220 has been provided for convenient soldering or laser welding of an exposed leadwire end 222.
  • the leadwire 1 24a would be of stranded insulated wire. One can see that the insulation has been removed by the leadwire end 222 so that it will contact soldering, the crimp 21 8, the laser weld 162, and a braze or thermal-setting conductive adhesive material 224.
  • FIGURE 24 is a cross-section taken generally from section 24-24 from FIG. 23. The cross-section is shown prior to crimping and shows that the hole 220 need not be round. In fact, a hole 220' in FIG. 24 is oval, but could also be elliptical, or any other shape. Also shown are a pair of optional internal indents 226 which are convenient when one places the terminal pin 200a and the leadwire 1 24a into place. The indents 226 stop the leadwire from pushing in too far so it can be properly located for crimping. [Para 1 22] Circuit junction connection 214 can be eliminated if the wires coming out of the hermetic seal 1 98 are made sufficiently long enough.
  • insulation tubing (not shown) would be placed over each of the leadwires 1 24a-l 24d (which in this case, become the same as the terminal pins 200a- 200d). Said tubing could also be non-conductive heat-shrink tubing. Then the EMI shield 206 could be slipped over the leadwires and then electrically connected to the AIMD electromagnetic shield housing 1 04 or to the conductive ferrule 1 38 of the hermetic seal 1 98.
  • the leadwires 1 24a-l 24d are inside the hermetically sealed AIMD electromagnetic shield housing 1 04, these leadwires 1 24a-l 24d do not need to be biocompatible. In fact, they can be low cost tinned copper or the like. This is important for ease of assembly and to keep the cost down of the overall assembly.
  • the filter capacitor component 21 0 of FIG. 21 has its outside diameter termination or metallization surface 1 50 (FIGS. 6 and 9) electrically and mechanically attached to the EMI shield 206. This provides a solid low impedance RF ground. Accordingly, the EMI shielded conduit assembly 1 96 becomes an extension of the overall electromagnetic shield of the AIMD electromagnetic shield housing 1 04.
  • the EMI shielded conduit assembly 1 96 could also be formed from low cost conductive (shielded) heat-shrink tubing.
  • the heat-shrink tubing would be heated to cause it to simultaneously be shrunk down over the four insulated leadwires 1 24a-l 24d, and at the same time be shrunk down around the outside diameter or perimeter of the ferrule 1 38 of the hermetic seal 1 98 to form the ground connection to the AIMD electromagnetic shield housing 104. It is very important that the overall coaxial or co-extensive EMI shield 206 be circumferentially and longitudinally nearly continuous and of very low inductance so that the EMI filter capacitor component 21 0 can provide proper attenuation at high frequencies.
  • the support feet 204 can alternatively be non-conductive, in which case they are simply there to provide mechanical attachment and resistance to shock and vibration loads. Or, as shown, the support feet 204 can be conductive and connect to the ground circuit traces 21 2a and 21 2b.
  • the ground circuit traces 21 2a and 21 2b are very useful for AIMD circuitry. For example, this low impedance ground can be used for connection of high voltage suppression arrays, such as diode arrays. As will be further illustrated, these ground circuit traces 21 2a and 21 2b are very useful to ground in or on an electronic circuit board, substrate or network.
  • the ground circuit traces 21 2a and 21 2b are also very useful for combinations of bandstop filters, L-C trap filters, low pass filters, electronic filters, a short-to-housing switch network, and the like. They could also be used for reference grounding or grounding of telemetry circuits and the like.
  • the EMI shield conduit in addition to shielding of the leadwires, also provides a low impedance circuit path for RF grounding of the remote EMI filter and/or other AIMD circuits.
  • FIGURE 22 is an end view taken generally from section 22-22 from FIG. 21 . Shown are the end views of the leadwires 1 24a-l 24d as they exit the filter capacitor component 21 0. One can also see the support feet 206 connected to the ground circuit traces 21 2a and 21 2b of the circuit board 202 (FIG. 21 ). In the case of a cardiac pacemaker, the circuit board 202 would also be known as the pacer hybrid board which contains various electronic modules, microelectronic chips, cardiac sense circuits and so on. Also shown are alternative via holes 228a-228d which connect to the leadwires 1 24a-l 24d. These can go to external or the interior circuit traces 230a-230d of the multilayer circuit board 202.
  • FIGURE 25 is very similar to the left side of FIG. 21 except that the novel EMI shielded conduit assembly 1 96 has been replaced by a conductive heat-shrink tubing 232.
  • a non-conductive heat-shrink insulation tubing 234 is slipped down over the leadwires 1 24a-l 24d as shown.
  • the insulation tubing 234 does not have to be heat-shrink tubing in this case. It could be a thin wall slip-on insulation tubing, such as Kapton or the like. Since the conductive ferrule 1 38 of the hermetic seal 1 98 is typically of titanium, it is prone to formation of oxides. These oxides can degrade electrical connections.
  • FIGURE 26 is the same view as FIG. 25 after heat has been applied to shrink the conductive heat-shrink tubing 232.
  • FIGURE 27 is an end view taken generally from section 27-27 from FIG. 26. It shows the end view of the four leadwires 1 24a-l 24d.
  • FIGURE 28 is a functional schematic diagram of the novel shielded conduit remote filter as previously discussed in FIGS. 21 through 27.
  • FIG. 28 there are four capacitors 238a-238d which are integral to the monolithic quadpolar feedthrough capacitor 1 76 illustrated in FIGS. 9-1 1 and 1 3.
  • the capacitors 238a-238d may be eliminated in certain AIMD designs where the AIMD internal unshielded leadwires or circuit traces are short in length compared to the wavelength of the EMI signals. In this case, the feedthrough capacitor would be eliminated and just the shielded conduit would be routed to the circuit board 202 as shown. This approach is particularly applicable to AIMDs that do not have sense circuits such as many implantable neurostimulators.
  • AIMDs that do not have biologic sense circuits are inherently less sensitive to EMI.
  • the leadwires 1 24a-l 24d illustrated in FIG. 28 are shown connected to the AIMD electronic circuit board, substrate or network 202 which can include a variety of electronic circuits including microchips.
  • the purpose of the quadpolar feedthrough capacitor 1 76 is to provide a single element low pass filter to ground on each leadwire 1 24a-l 24d in order to protect the sensitive electronics on the circuit board 202 from EMI that can be coupled from the implanted leads 1 22a-l 22d. This is particularly important if the AIMD electronic circuit board, substrate or network 202 has biologic sensing circuits which is common in the prior art for cardiac pacemakers and ICDs.
  • FIGURE 29 illustrates a particular type of EMI shield 206 called braid shielding.
  • a set of fine wires 240 are woven back and forth underneath an insulated surface 242 (transparent) as shown.
  • FIGURES 30 and 31 show that the novel EMI shielded conduit assembly 1 96 can be of solid material such as soft copper.
  • FIG. 30 is an end view illustrating the solid tubing of the EMI shielded conduit assembly 1 96 and the unipolar leadwire 1 24 disposed within an insulative material 244. The insulative or dielectric material 244 is used as shown.
  • FIGURE 32 illustrates the use of a coaxial wound wire 246 to form the EMI shield 206.
  • FIGURE 33 shows the use of a metallic thin conductive foil, or foils, 248 which can be formed, wound, or woven around the insulative material 244 to form the EMI shield 206 around the leadwire 1 24.
  • FIGURE 34 is very similar to FIG. 30, but shows four leadwires 1 24a-l 24d.
  • FIGURE 35 illustrates a shielded mesh 250 interwoven with a set of conductive strands 252 (FIG. 76).
  • FIGURE 36 is an enlarged view of area 36 in FIG. 35 showing how the conductive strands 252, 252' are woven. It is very important that the weaving be fairly tight so stray high frequency EMI cannot penetrate the shield and that the inductance of the shield conduit be relatively low.
  • FIGURE 37 shows an alternative embodiment of the EMI shielded conduit assembly 1 96 that was previously shown in FIG. 21 .
  • the filter capacitor component 21 0 that was shown in FIG. 21 could still be used, but it would be mounted on the circuit board 202 in place of the four MLCC chip capacitors 1 28a-l 28d shown in FIG. 37.
  • the filter capacitor component 210 would ideally be mounted face down on the circuit board 202 with its outside diameter ground metallization 1 50 (FIG. 9) electrically attached to a surrounding ground plane 254 which is also connected to the proximal end of the EMI shielded conduit assembly 1 96. Referring once again to FIG.
  • the leadwires 1 24a-l 24d are routed within the overall EMI shielded conduit assembly 1 96 to the left hand side of the prior art MLCC chip capacitors 1 28a-l 28d.
  • the conductive support foot assembly 204 is shown electrically and mechanically connected to a ground plane 254.
  • This ground plane 254 is desirably wide and continuous so it will form an effective low impedance high frequency equipotential surface.
  • the right hand side of the prior art MLCC chip capacitors 1 28a-l 28d are electrically connected to this ground plane 254. Referring once again to FIG. 37, one can see that the ground plane circuit trace 254 is electrically connected to the EMI shielded conduit assembly 1 96.
  • this circuit path be very low in impedance. That is, it is important that at high frequency, the surface of the ground plane 254 be held at approximately the same potential as the overall AIMD electromagnetic shield housing 104.
  • the EMI shielded conduit assembly 1 96 must be of relatively large cross-sectional area. This can be imagined if one were to slit it and then roll it out flat and look at it from edge view. This forms, in the art, an equivalent RF grounding strap.
  • the novel EMI shielded conduit assembly 1 96 forms two very important purposes: (1 ) it effectively shields and prevents EMI re-radiation inside the AIMD housing from the leadwires 1 24a-l 24d; and (2) it provides a very low impedance connection back to the AIMD electromagnetic shield housing 104 to the circuit board ground path 254.
  • the leadwires 1 24a-l 24d are electrically connected through the via holes 228a-228d using an electrical connective material 256-256'", such as solder or thermal-setting conductive adhesive.
  • the MLCC capacitors 1 28a-l 28d are also electrically connected to the ground plane 254 through electrical connections 256-256'".
  • the shielded support foot 204 is in the form of a ring and is electrically connected either through holes 258 or by way of an outside electrical connection 260 as shown. It is important that the portion of the leadwires 1 24a-l 24d that exits the EMI shielded conduit assembly 1 96 be kept quite short so they will not become an effective re-radiating antenna or stray capacitance which would allow EMI to couple to sensitive circuits such as pacemaker sense circuits.
  • the assemblies shown in FIG. 37 are all mounted to the AIMD electronic circuit board, substrate or network 202 which supports other surface mounted or imbedded AIMD electronic components (not shown).
  • the via holes 228a-228d connect to internal circuit traces 230a-230d as shown.
  • FIGURE 38 is a schematic diagram of the remote MLCC chip capacitor 1 28 as illustrated in FIG. 37. Referring to FIG. 38, one can see on the left side the hermetic terminal 100. Its ferrule 1 38 is coupled to a ground 262, which is coupled to the overall AIMD electromagnetic shield housing 1 04.
  • the EMI shielded conduit assembly 1 96 is also shown electrically grounded to the hermetic terminal 1 00. It is important that this be a low impedance oxide free connection. This connection from the EMI shielded conduit assembly 1 96 can be accomplished by a clamp (not shown) which binds the conductive EMI shielded conduit assembly 1 96 to the outside diameter of the ferrule 1 38.
  • the titanium ferrule 1 38 of the hermetic terminal 100 would be pretreated with plating, gold braze, or the like to prevent oxidation.
  • An alternative would be to solder, braze or attach with conductive adhesives the EMI shielded conduit assembly 1 96 to the ferrule gold braze of the hermetic seal assembly (ref. the methods described in U.S. 6,765,779, the contents of which are incorporated herein).
  • the remote EMI filter (or optionally an unfiltered circuit board), in this case, consists of the four MLCC chip capacitors 1 28a-l 28d as shown. These also form in the art what is known as a quadpolar single element low pass filter.
  • An optional inductor element 264 has been shown in the leadwire 1 24a.
  • L, Pl, T, LL or "n" element low pass filters in any or all leadwires 1 24a-l 24d.
  • the high voltage suppression array 266 can consist of back-to-back diodes 268a and 268b as shown, zener diodes, Transorbs ® , and the like. It is important that the high voltage suppression diodes have a low impedance connection to a circuit ground 270 so they can be fast acting.
  • FIG. 38 An important feature of the EMI shielded conduit assembly 1 96 is that it provides the required low impedance circuit path to ground.
  • the MLCC capacitors 1 28a-l 28d are all connected to the conduit circuit ground 270 and in a preferred embodiment, the high voltage suppression array 266 is also connected to the same low impedance circuit ground 270 as shown.
  • FIGURE 39 is generally taken from section 39-39 in FIG. 37.
  • FIG. 39 Shown is a multi-element chip capacitor monolithic array 272 which is better understood by referring to an internal active electrode 274a-274d and an internal ground electrode 276 in FIGS. 40 and 41 .
  • the capacitor array 272 of FIG. 39 is very similar to prior art MLCC chip capacitors, but the single quadpolar chip is more volumetrically efficient. This is accomplished by placing all four chip capacitors in a single monolithic package.
  • the multi-element chip capacitor monolithic array 272 shown in FIG. 39 can also be replaced by the flat-through capacitor 1 90 as shown in FIGS. 1 7 through 20, an active electronic filter, or even an X2Y attenuator.
  • An X2Y attenuator is generally a specially configured ceramic chip capacitor with unique internal electrode geometry.
  • FIGURES 42 to 53 show various circuit schematic combinations which illustrate a number of ways that the novel EMI shielded conduit assembly 1 96 may be configured with remote circuit boards/substrates 202, low pass filters LP, BSFs, L-C traps, active electronic filters, high voltage suppression (circuit protection) arrays, and electronic short-to-housing switch networks.
  • remote circuit boards/substrates 202 low pass filters LP, BSFs, L-C traps, active electronic filters, high voltage suppression (circuit protection) arrays, and electronic short-to-housing switch networks.
  • U.S. Patent Application No. 1 2/489,921 for examples of how such electronic components can be advantageously used in connection with the present invention.
  • FIGURES 42 to 52 are all illustrated for one leadwire 1 24 or circuit path of the AIMD only.
  • the AIMD can have any number of circuit leadwires 1 24 that are routed through one or more hermetic seal 1 98 terminal pins 200 to the implanted leads 1 22 to which the present invention applies.
  • FIG. 42 illustrates the case with no passive low pass filter where the circuit traces 21 2 a to 21 2 n are short relative to the EMI frequency wavelength and/or the AIMD is not very sensitive to EMI.
  • FIGURE 43 illustrates an inductor 264 single element low pass filter 280.
  • FIGURE 44 illustrates what is known in the prior art as an "L" section low pass filter 282 consisting of the inductor 264 and the capacitor 238. In this case, the inductor 264 points toward the hermetic seal (body fluid side).
  • FIGURE 45 is a reverse "L” low pass filter 284 where the capacitor 238 points toward the hermetic seal (body fluid side).
  • FIGURE 46 is known in the art as a "T” filter 286.
  • FIGURE 47 is known as a Pl filter 288.
  • FIGURE 48 generally shows an n-element low pass filter 290. Either the inductor (264a as shown) or the capacitor 238a can be the first component on the hermetic seal (body fluid side).
  • FIGURE 49 illustrates a bandstop filter (BSF) 292 in series with the leadwire 1 24 consisting of the inductor 264 and the capacitor 238 in parallel (there can also be a resistive element, which is not shown).
  • BSF bandstop filter
  • FIGURE 50 illustrates an L-C trap filter 294.
  • the L-C trap filter 294 connects from the leadwire 1 24 to the low impedance circuit ground 262 and consists of the capacitor 238 in series with the inductor 264 (there can also be a resistive element, which is not shown).
  • U.S. 6,424,234 which is herein incorporated by reference, for a full explanation of L-C trap filter characteristics, resonance equations, bandwidth and impedance vs. frequency curves.
  • FIGURES 51 and 52 illustrate that any of the low pass filters 280- 284 and 290 can be wired in various combinations with the BSF filter 292 and/or the L-C trap filter 294 to form any passive filter that one wishes to realize.
  • the EMI shielded conduit assembly 1 96 forms the circuit ground 262 for the circuit board 202, the low pass filter 280- 284 and 290, the L-C trap filter 294, the high voltage suppression array 266, a telemetry circuit, a general circuit board/substrate reference (this is particularly important when the AIMD housing becomes a pacing or sensing electrode), an active electronic filter circuit, and/or the RF low impedance ground for a short- to-housing switch network.
  • combining any of the low pass filters 280-284 and 290 with the bandstop filters 292 and/or the L-C trap filters 294 can be very effective for MRI environments.
  • FIGURE 53 illustrates an automatic or programmable electronic short-to-housing switch network chip or electronic switch array which can be a dedicated chip or a portion of the hybrid or microchip of the AIMD which forms many other functions.
  • Electronic switches which form a short to the AIMD housing are more fully described in U.S. Patent Application No. 1 2/489,921 .
  • the electronic switch array 296 of FIG. 53 would have its switches normally closed (in FIG. 53, they are shown in the open position). This allows the AIMD to operate normally, sense biologic signals, and delivery needed therapy such as pacing pulses to body tissue.
  • the switches are shown in FIG.
  • the wipers of the switches 298a-298d are connected toward the hermetic terminal 1 00 (body fluid) side of the leadwires 1 24a-l 24d.
  • the wipers are connected to the circuit ground 270" which is provided by the novel EMI shielded conduit assembly 1 96.
  • the leadwires 1 24a-l 24d are disconnected from other AIMD electronic circuits.
  • the wiper connection forms a low impedance RF ground which shorts out each one of the leadwires 1 24a-l 24d effectively through the EMI shielded conduit assembly 1 96 to the AIMD electromagnetic shield housing 104.
  • the switches 298a-298d can have mechanical wipers, however, in the preferred embodiment, these would be any type of electronic switches such as involving P-N junctions well known in the prior art.
  • the switches would be controlled (programmed) through AIMD programming and telemetry. With a field sensor, the switches could also be configured to switch automatically, say in the presence of a powerful magnetic field such as the static Bo field of an MRI scanner. For a patient who was not dependant on their AIMD as a life saving device (most neurostimulator patients, and non-pacemaker dependant pacemaker patients), the switch array ESA would be used when the AIMD and/or its implanted leads are exposed to powerful electromagnetic fields, such as those produced by a clinical MRI scanner.
  • the electronic switch array is easily programmed into its MR Conditional Mode prior to the MRI scan. This mode switches the switches 298a-298d in the electronic switch array to the open (shorted position) as shown in FIG. 53.
  • the AIMD could also be programmed into an quiescent mode wherein it was not trying to sense biologic signals or deliver therapeutic pulses. [Para 141 ] During the MRI (or other field exposure), the position of the switches 298a-298d shown in FIG. 53 accomplishes two very important things. The first is that the sensitive electronic circuitry (not shown) of the AIMD is disconnected and therefore becomes highly resistant to being influenced by EMI from the MRI scanner (or other high energy EMI source).
  • the second major advantage is the shorting of the leadwires 1 24 to the low impedance EMI shielded conduit (circuit ground). This will pull unwanted induced RF energy out of the implanted leadwires 1 24 and divert said energy to the large surface area of the AIMD housing. This will greatly help to reduce implanted distal electrode heating at the points of tissue interface. By dissipating the induced MRI RF energy over the relatively large surface area of the AIMD electromagnetic shield housing 1 04, only a few degrees of harmless thermal energy will occur. This is in contrast to 20 or 30 degrees (or more) of possible temperature rise at the distal electrodes of the elongated implanted leadwires 1 24 without these features.
  • FIG. 53 Another advantage of the electronic switch array ESA configuration illustrated in FIG. 53 is that the induced RF MRI energy that is picked up by the implanted leads 1 22 is diverted to the AIMD electromagnetic shield housing 1 04 which is usually not implanted in an area of the human body that is as sensitive to thermal injury.
  • the AIMD electromagnetic shield housing 1 04 which is usually not implanted in an area of the human body that is as sensitive to thermal injury.
  • a cardiac pacemaker a spinal cord stimulator or a deep brain stimulator
  • the novel EMI shielded conduit assembly 1 96 works in conjunction with the electronic switch array 296.
  • FIGURE 54 illustrates a prior art quadpolar hermetic terminal 300 with a conductive ferrule 302. Shown are four hermetic seal terminal pins 200- 200'" and a prior art flex cable 304 with circuit traces 306a-306d that are routed to a circuit board or substrate 202. This is a prior art attempt to provide EMI filtering through MLCC capacitors 1 8Oa-I 8Od. There is a ground connection 308 which grounds the circuit substrate. There are many attempts in the prior art to form an exposed flex cable or leadwire configuration as shown in FIG. 54. Due to lack of shielding and a high impedance ground path (loop) these attempts result in very poor EMI filter performance of the overall AIMD.
  • circuit path of the circuit traces 306a-306d is relatively long compared to the wavelength of most EMI energy. Therefore, these circuit traces 306a-306d become very effective re-radiating antennas. This is called “the genie in the bottle” affect.
  • the EMI gets inside the overall AIMD shielded housing, it can cross-couple or re-radiate to adjacent sensitive circuits, such as pacemaker biologic sense circuits.
  • another problem associated with the prior art arrangement shown in FIG. 54 arises due to the narrowness of the circuit traces 306a-306d and their relatively long length 310, which creates substantial inductance and impedance.
  • FIGURE 55 is a cross-sectional view of an improved flex cable 304' incorporating the novel features described herein, and is very similar to FIG. 54.
  • the circuit trace 306 has been imbedded between a top shield plane 31 2 and a bottom shield plane 314.
  • a parasitic capacitance is desirably formed between the circuit trace 306 and the surrounding ground shield planes 314, 316. This aids in high frequency filter attenuation.
  • FIG. 55 forms an EMI shield extension of the overall AIMD electromagnetic shield housing 1 04.
  • FIGURE 56 illustrates the flex cable 304' from FIG. 55 attached to circuit board 202. Shown is a surface mounted flat-through capacitor 1 90'.
  • the flat-through capacitor 1 90' is very similar to the unipolar flat-through capacitor 1 90 shown in FIGS. 1 7 and 1 8, but is different in that the flat-through capacitor 1 90' of FIG. 56 has four capacitors with a single ground plane 31 8.
  • An active electrode plate set (AEP) 31 8 for the flat-through capacitor 1 90' of FIG. 56 is shown in FIGURE 57.
  • a pair of metallization surfaces 320 and 320' correlate to those indicated in FIG. 56.
  • a ground electrode plate (GEP) 322 is illustrated in FIGURE 58.
  • ground electrode plates 31 8, 322 of FIGS. 57 and 58 these would typically be stacked up and interleaved to achieve the desired effective capacitance area (ECA).
  • ECA effective capacitance area
  • the flat-through capacitor 1 90' can be replaced or used in combination with prior art circuit board electronics, prior art high voltage suppression arrays, X2Y attenuators, other potential low pass filters, active filters and even electronic short-to-housing switch networks.
  • the leadwires 1 24a- 1 24d relatively short as they exit the shielded flex 304', one can prevent re- radiation or cross-coupling to adjacent circuits at high frequency.
  • ANSI/AAMI Standard PC69 describes radiated tests in the 450 to 3000 MHz range.
  • FIGURE 59 is generally taken from section 59-59 of FIG. 55. Shown are the circuit traces 306a-306d.
  • FIGURE 60 is taken from the two layers 60-60 of FIG. 55. Accordingly, the circuit traces 306a-306d are sandwiched between the ground shield plates 326, 326' top to bottom as illustrated in FIG. 60.
  • the ground shield plates 326, 326' of FIG. 60 serve to effectively shield the imbedded circuit traces 306a-306d from EMI. Further, the ground shield plates 326, 326' form a very low impedance path from the electronic circuit board, substrate or network 202 back to the AIMD electromagnetic shield housing 104.
  • FIGURE 61 is generally taken from layer 61 -61 of FIG. 55. This is very similar to FIG.
  • FIGURE 62 illustrates a bottom shield ground electrode plate 332 of the flex cable 304' from FIG. 55 and FIG. 56.
  • a robot has dispensed a circular portion of a thermal-setting conductive material 334. This is designed to align precisely with the gold braze 1 58 of the hermetic terminal 1 00 of FIGURE 63. Accordingly, the entire left end of the shielded flex cable 304' can be laid down over the hermetic terminal 1 1 0 and then the thermal- setting conductive material 334 can be cured in an oven, furnace or other equivalent process. This makes a suitable electrical and mechanical connection to the exposed bottom ground shield electrode plate 332. Referring back to FIG.
  • FIGURE 63 is a sectional view of the hermetic seal 100 taken along line 63-63 from FIG. 55.
  • BGA ball grade array
  • internal pins 1 24' and 1 24'" could have headed leads in the location of gold braze GBS (for example, see FIGS. 9 and 10 of U.S.
  • FIGURE 64 illustrates a novel laser weld cap 336 with a cut out section 338.
  • the cut out section 338 is formed or cut so the metal laser weld cap 336 can slip down over a narrow section 340 of the end of the flexible portion of the shielded flex cable 304'.
  • the laser weld cap 336 can be a stamped titanium, machined titanium, injection molded titanium or a number of other metals.
  • FIGURE 65 is a combined cross-section taken generally from 63-63 of FIG. 55 and also from section 65-65 of FIG. 64.
  • the shielded flex cable 304' has been modified to accommodate the novel laser weld cap 336 as illustrated in FIG. 64.
  • the laser weld cap 336 is slipped down such that it comes into close contact with a flange 342 of the hermetic terminal 1 00.
  • a continuous or discontinuous laser weld or braze 344 is formed as shown. This makes a solid metallurgical and low impedance ground contact to the hermetic flange 342 and to the laser weld cap 336.
  • ground shield plates 326 and 326' are external for the purposes of this illustration; however, they could be internal plates as previously illustrated.
  • FIGURE 66 shows a hermetic terminal assembly 1 00.
  • the hermetic terminal subassembly 100 consists of a metallic ferrule 1 38 which is generally made of titanium.
  • the ferrule 1 38 is gold brazed 1 58 and 1 58' to the alumina ceramic insulator 1 56 as shown.
  • Gold brazes 1 58' and 1 58" form a hermetic seal between the insulator 1 56 and the leadwires 1 24a- 1 24d.
  • an insulating sleeve 352 is slipped down over the leadwire 1 24 into the inside diameter of the protrusion 350. This is seated against the bottom adjacent to gold braze 1 58' or 1 58".
  • the insulating sleeve 352 can be a close-fitting semi-flexible insulation sleeve or it can be a non-conductive heat-shrink tubing. In the case of heat-shrink tubing, the sleeve would be placed down as shown and then heat would be applied to shrink it in place firmly against the leadwire 1 24.
  • the EMI shielded conduit assembly 1 96 would be slipped down over the outside of the protrusion 350.
  • the cap assembly 348 would be electroplated or coated so that there are no issues with oxides.
  • the cap assembly 348 can also be of suitable materials that do not form oxides. It is very important that the conductive coaxial or coextensive EMI shielded conduit assembly 1 96 form a low impedance short-to- housing electrical connection to the end cap protrusion 350.
  • the EMI shielded conduit assembly 1 96 would be a conductive heat-shrink tubing and would be slipped down over the protrusion 350, heat would then be applied so that the tubing 354 is shrunk down and firmly adhered to the protrusion 350 of the cap assembly 348.
  • the heat-shrink tubing 354 is shown in its preshrunk condition. Accordingly, there is a gap 356 between the conductive EMI shield and the insulating sleeve 352. After applying heat, the heat-shrink tubing 354 would shrink down so that it also bonded against the insulating sleeve 352.
  • the cap assembly 348 can be attached to the ferrule 1 38 of the hermetic terminal 1 00 by laser welding 162, by soldering to the gold braze 1 58, or by using various thermal-setting conductive adhesives that would connect between the cap assembly 348 and the gold braze 1 58. In all cases, it is also important that this be an oxide-free connection.
  • the novel cap assembly 348 illustrated in FIG. 66 enables the leadwires 1 24a-l 24d to be routed to different locations inside of the AIMD electromagnetic shield housing 1 04. In other words, as illustrated, leads 1 24a, 1 24b can be routed off to the right and leads 1 24c, 1 24d can be routed to another location. This is important in modern AIMDs which can have as many as twelve or more leadwires and multiple electronic circuit boards or substrates.
  • FIGURE 67 is taken generally from section 67-67 in FIG. 66.
  • FIG. 67 illustrates the details of the cap assembly 348 that has a through hole 358.
  • One or more through holes 358 can be provided for convenient brazing or laser welding. This would be very useful if the metallic shielding was of the type as previously illustrated in FIG. 32 or 33. This is also particularly suitable if the EMI shielded conduit assembly 1 96 is of braided shield wire.
  • FIGURE 68 illustrates a novel application of a cylindrical or coaxial shielded conduit 360 attached to a stamped or machined metallic lid cover 362. The lid cover 362 makes a transition from coaxial to rectangular geometry.
  • hermetic terminal assembly 364 which is known as an inline octa-polar (8-pin) assembly.
  • Leadwires 1 24, in this case, 1 24a-l 24h, are attached using a splice or the previously described circuit junction connection 214. This would be shown eight times attached to the terminal pins 200.
  • the hermetic insulator has a set of gold braze pads 366 that are designed to mate with the mounting tabs and holes 368 of lid cover 362. In manufacturing, first the connection to the terminal pins 200 is made using the circuit junction connectors 214, then the lid cover 362 and the EMI shielded conduit assembly 1 96 along with its associated attached coaxial shielded conduit 360 is pressed down and seated onto the gold braze pads 366.
  • FIGURE 69 illustrates the full length of the EMI shielded conduit assembly 1 96 previously described in FIG. 68. Shown on the left is the stamped lid cover 362 and on the right is the coaxial shielded conduit 360. The EMI shielded conduit assembly 1 96 is electrically and mechanically attached to both the coaxial shielded conduit 360 and the lid cover 362. The assembly shown in FIG. 69 can be preassembled and pre-tested such that it is ready for attachment to the hermetic seal 1 98 and a circuit board 202 (not shown). [Para 1 59] FIGURE 70 is taken from FIGS.
  • the circuit junction connection 214 is used to attach to a substrate or even a feedthrough capacitor 370 as shown. After the leadwires 1 24 pass through the feedthrough capacitor 370, they are then attached to the circuit traces 21 2 on the circuit board 202. Referring to FIG. 70, one can see a pair of metallization surfaces 372 and 372' on the feedthrough capacitor 370. These correspond with connections to the feedthrough capacitor 370 internal ground electrode plates (GEP) 374 as illustrated in FIGURE 71 .
  • the metallization surface 372 is designed to be soldered to the lid cover 362'.
  • FIGURE 72 A set of active electrode plates AEP 377 of the feedthrough capacitor 370 are illustrated in FIGURE 72.
  • FIGURE 73 illustrates an alternative to FIG.
  • FIGURES 74 and 75 illustrate an active electrode plate set (AEP) 384 and a ground electrode plate set (GEP) 386 of the flat-through capacitor 378, respectively.
  • AEP active electrode plate set
  • GEP ground electrode plate set
  • FIG. 73 is particularly suitable where microwave high frequency EMI is a concern. This is a completely shielded assembly which allows no possible leakage of high frequency EMI around the flat-through capacitor 378'.
  • FIGURE 76 illustrates yet another alternative to the designs previously described in FIGS. 70 and 73.
  • the novel flat-through capacitor 378' shown in cross-section in FIG. 76 is designed to be installed and have its outside perimeter metallization electrically and mechanically connected directly to the inside or a surface of the lid cover 362.
  • Leadwires 1 24 are connected to a through hole in the novel flat-through capacitor 378' and electrically connected at location 388 as shown.
  • a short pin 390 is electrically connected on the other side of the flat-through capacitor 378' at electrical location 392.
  • This pin 390 can be soldered to a circuit land wire bond pad or through the via hole 382, as shown, to connect to the electric circuit traces 21 2 of the circuit board 202.
  • the cross-sectional view as illustrated in FIG. 76 completely stops any re-radiation of EMI inside the AIMD housing and will work at very high frequency.
  • FIGURE 77 is an end view of the flat-through capacitor 378' taken from FIG. 76.
  • FIG. 78 illustrates an active electrode plate (AEP) 394 of the flat- through capacitor 378' described in FIG. 76.
  • FIG. 79 illustrates a ground electrode plate (GEP) 396 of the novel flat-through capacitor 378' of FIG. 76.
  • AEP active electrode plate
  • GEP ground electrode plate
  • the present invention enables the mounting of RF sensitive components at a distance remote from the hermetic terminal by providing a novel EMI shielded conduit assembly which also provides a very low impedance or RF ground to the circuit board.
  • the AIMD housing has a much larger surface area when compared to an implanted electrode, it is capable of dissipating energy without significant temperature rise over this large surface area. This protects against tissue damage that can be caused by excessive energy (heat) being deposited in leads and/or electrodes in contact with body tissue.
  • the present invention eliminates the need to mount a low pass filter or other components on or adjacent to the hermetic terminal for the AIMD housing, and instead allows the position of the desired filter or other components on a remote electronic circuit board, substrate or network. Moreover, in some instances, the present invention eliminates altogether the need for the low pass filter and its associated size and complexity by providing a low inductance conductive extension of a equipotential housing.
  • An important feature of the present invention is that it also reduces the effective unshielded lead length of leadwires routed from the hermetic terminal inside the AIMD housing. That is, by providing an overall shield around most of or all the length of these internal leadwires, their effective wavelength is reduced. Therefore, they become very ineffective re-radiating or coupling antennas. By keeping electronic circuit board, substrate or network circuit trace elements relatively short, they also do not become effective antennas below 3 GHz. For this reason, in certain AIMD embodiments, one does not even require the use of filter capacitors or multi-element low pass filters. This is particularly true of AIMDs that do not sense, such as most neurostimulators.

Abstract

L'invention porte sur un ensemble conduit blindé contre les interférences électromagnétiques pour dispositif médical implantable actif (AIMD), comprenant une enceinte protégée contre les interférences électromagnétiques pour l'AIMD, une borne hermétique d'alimentation associée à l'enceinte AIMD et une carte imprimée électronique, un substrat ou un réseau disposé dans l'enceinte AIMD à distance de la borne hermétique d'alimentation. Au moins un fil conducteur s'étend à partir de la borne hermétique d'alimentation jusqu'à la carte de circuit distante, le substrat ou le réseau. La gaine de blindage contre les interférences électromagnétiques est couplée de manière conductrice à l'enceinte AIMD et s'étend sensiblement autour du fil conducteur et en association avec lui dans une relation non conductrice avec celui-ci.
PCT/US2010/027677 2009-03-19 2010-03-17 Ensemble conduit blindé contre les interférences électromagnétiques pour dispositif médical implantable actif (aimd) WO2010107926A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP10754066A EP2408520A4 (fr) 2009-03-19 2010-03-17 Ensemble conduit blindé contre les interférences électromagnétiques pour dispositif médical implantable actif (aimd)

Applications Claiming Priority (12)

Application Number Priority Date Filing Date Title
US12/407,402 US8195295B2 (en) 2008-03-20 2009-03-19 Shielded three-terminal flat-through EMI/energy dissipating filter
US12/407,402 2009-03-19
US12/489,921 US7751903B2 (en) 2002-04-15 2009-06-23 Frequency selective passive component networks for implantable leads of active implantable medical devices utilizing an energy dissipating surface
US12/489,921 2009-06-23
US26641109P 2009-12-03 2009-12-03
US61/266,411 2009-12-03
US28933209P 2009-12-22 2009-12-22
US61/289,332 2009-12-22
US12/686,137 2010-01-12
US12/686,272 US8509913B2 (en) 2001-04-13 2010-01-12 Switched diverter circuits for minimizing heating of an implanted lead and/or providing EMI protection in a high power electromagnetic field environment
US12/686,137 US8989870B2 (en) 2001-04-13 2010-01-12 Tuned energy balanced system for minimizing heating and/or to provide EMI protection of implanted leads in a high power electromagnetic field environment
US12/686,272 2010-01-12

Publications (1)

Publication Number Publication Date
WO2010107926A1 true WO2010107926A1 (fr) 2010-09-23

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EP (1) EP2408520A4 (fr)
WO (1) WO2010107926A1 (fr)

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US8219208B2 (en) 2001-04-13 2012-07-10 Greatbatch Ltd. Frequency selective passive component networks for active implantable medical devices utilizing an energy dissipating surface
US8275466B2 (en) 2006-06-08 2012-09-25 Greatbatch Ltd. Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices
EP3261117A1 (fr) 2016-06-22 2017-12-27 Commissariat à l'Energie Atomique et aux Energies Alternatives Boitier de dispositif microélectronique

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Cited By (5)

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Publication number Priority date Publication date Assignee Title
US8219208B2 (en) 2001-04-13 2012-07-10 Greatbatch Ltd. Frequency selective passive component networks for active implantable medical devices utilizing an energy dissipating surface
US8275466B2 (en) 2006-06-08 2012-09-25 Greatbatch Ltd. Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices
US9119968B2 (en) 2006-06-08 2015-09-01 Greatbatch Ltd. Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices
EP3261117A1 (fr) 2016-06-22 2017-12-27 Commissariat à l'Energie Atomique et aux Energies Alternatives Boitier de dispositif microélectronique
US10173890B2 (en) 2016-06-22 2019-01-08 Commissariat A L'energie Atomique Et Aux Energies Alternatives Microelectronic device housing bearing on the microelectronic device

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Publication number Publication date
EP2408520A1 (fr) 2012-01-25
EP2408520A4 (fr) 2012-12-19

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