阅读说明：本技术 经选择的同时刺激 (It is seleced to stimulate simultaneously ) 是由 T·莱曼 T·尼加德 于 2018-04-16 设计创作，主要内容包括：本文提出了诸如组织刺激假体的可植入医疗设备,其被配置为将同时的刺激递送给接受者。在一个实施例中,组织刺激假体包括多个电流源、多个电极(例如,电极的线性阵列)以及开关的硬接线电网络,该开关的硬接线电网络在本文中有时被称为“稀疏开关网络”。稀疏开关网络被配置为将电流源中的每个电流源连接到一个以上的电极,并且将电极中的每个电极连接到电流源的仅一个子集。稀疏开关网络被配置为防止相邻的电极连接到相同的电流源。(This paper presents the implantable medical device of such as tissue stimulation prosthese, it is configured as stimulation simultaneously being delivered to recipient.In one embodiment, tissue stimulation prosthese includes the hardwire electric network of multiple current sources, multiple electrodes (for example, linear array of electrode) and switch, and the hardwire electric network of the switch is herein referred to as " sparse switching network ".Sparse switching network is configured as each current source in current source being connected to more than one electrode, and each electrode in electrode is connected to the only one subset of current source.Sparse switching network is configured as that adjacent electrode is prevented to be connected to identical current source.)

1. a kind of implantable medical device, comprising:

Current source is configurable to generate the stimulus signal of the recipient for delivery to the implantable medical device；

The array of stimulating electrode；And

Multiple switch is configured as each current source in multiple current sources being selectively electrically connected to multiple thorns Swash electrode,

Wherein the multiple switch is arranged to adjacent stimulating electrode is prevented to be connected to identical in multiple current sources Current source.

2. implantable medical device according to claim 1, wherein the multiple switch is arranged to the stimulation electricity Each stimulating electrode in extremely is used to selectively connect to the only one subset in multiple current sources, and being arranged to will be more Each current source in a current source is used to selectively connect to the only one subset of the stimulating electrode.

3. implantable medical device according to claim 1, wherein the multiple switch is arranged to the stimulation electricity Each stimulating electrode in extremely is connected to the only single current source in multiple current sources.

4. implantable medical device according to claim 1, wherein the multiple switch is arranged to the stimulation electricity Each stimulating electrode in extremely is connected to only two current sources in multiple current sources.

5. implantable medical device according to claim 1, wherein the multiple switch is arranged to prevent the stimulation The connection between at least one current source in each stimulating electrode and multiple current sources in electrode.

6. implantable medical device according to claim 1, wherein the multiple switch is arranged to the stimulation electricity The subset of pole is concomitantly connected at least one subset of multiple current sources, and the wherein son of the stimulating electrode Collection includes one group of sequence stimulating electrode from the array.

7. implantable medical device according to claim 1, wherein each stimulating electrode in the stimulating electrode is connected The single switch being connected in the multiple switch.

8. implantable medical device according to claim 1, wherein the multiple switch is in multiple current sources and institute Stating has hardwire mode between stimulating electrode.

9. implantable medical device according to claim 1, in which:

Each stimulating electrode in the stimulating electrode is connected to multiple institutes via a switch in the multiple switch The single current source in current source is stated, and

Multiple current sources are sequentially connected to the stimulating electrode in the array, and wherein catenation sequence is along described Array repeats.

10. implantable medical device according to claim 1, wherein each switch in the multiple switch be high side/ Low side switch.

11. a kind of tissue stimulation prosthese, comprising:

Multiple electrodes；

Multiple current sources；And

Sparse switching network, is configured as: each current source in the current source is connected to one in the electrode by (i) Above electrode, and each electrode in the electrode is connected to the only one subset in the current source by (ii).

12. tissue stimulation prosthese according to claim 11, wherein the sparse switching network includes multiple switch, and Wherein an electrode in the electrode is connected to a current source in the current source by each switch in the switch.

13. tissue stimulation prosthese according to claim 11, wherein the number of the current source is less than the number of the electrode Mesh.

14. tissue stimulation prosthese according to claim 11, wherein the multiple current source include multiple master current sources and Auxiliary current source, and wherein the sparse switching network is configured as each electrode in the multiple electrode selectively The only one master current source being connected in the master current source, and all electrodes in the electrode are used to selectively connect to The auxiliary current source.

15. tissue stimulation prosthese according to claim 11, wherein the sparse switching network includes multiple switch, it is described Multiple switch has hardwire mode between the current source and the electrode.

16. tissue stimulation prosthese according to claim 11, wherein the sparse switching network is configured as the electricity The subset of pole is concomitantly connected at least one subset of the current source.

17. tissue stimulation prosthese according to claim 16, wherein the multiple electrode is set with linear array, and Wherein the subset of the electrode includes one group of sequence electrode.

18. tissue stimulation prosthese according to claim 16, wherein the multiple electrode is set with linear array, and Wherein the subset of the electrode includes one group of electrode, and one group of electrode is respectively each other by least one dispersing electrode It separates.

19. tissue stimulation prosthese according to claim 11, wherein the multiple switch is arranged to prevent the electrode In each electrode and the current source at least one current source between connection.

20. a kind of tissue stimulation prosthese, comprising:

Multiple current sources, wherein each current source in the current source is configured as generating electrical stimulation signal；And

The array of stimulating electrode, wherein the stimulating electrode is configured as to deliver from the received electrical stimulation signal of the current source To the tissue of recipient；And

Each current source in the current source is connected to the stimulating electrode by hardwire electric network, the hardwire electric network Only one subset.

21. tissue stimulation prosthese according to claim 20, in which:

The hardwire electric network includes multiple switch, and

A stimulating electrode in the stimulating electrode is connected in the current source only by each switch in the switch One current source.

22. tissue stimulation prosthese according to claim 20, wherein the hardwire electric network will be in the current source Each current source is connected to the more than one stimulating electrode in the stimulating electrode.

23. tissue stimulation prosthese according to claim 20, wherein be configured as will be adjacent for the hardwire electric network Stimulating electrode is decoupled from identical current source, and is configured as realizing and from the current source while being delivered to electrical stimulation signal The sequence stimulating electrode of the array.

24. tissue stimulation prosthesis apparatus according to claim 20, wherein the hardwire electric network is configured as preventing The connection between at least one current source in each stimulating electrode and the current source in the stimulating electrode.

25. tissue stimulation prosthesis apparatus according to claim 20, wherein the multiple current source includes multiple principal currents Source and auxiliary current source, and wherein the hardwire electric network is configured as each stimulation in the multiple stimulating electrode Electrode is used to selectively connect to the only one master current source in the master current source, and by institute's spinosity in the stimulating electrode Sharp electrode is used to selectively connect to the auxiliary current source.

Technical field

Present invention relates in general to tissue stimulation prostheses.

Background technique

There is the implantable medical device of several types, by passing to the nerve of recipient, muscle or other tissue fibers Power transmission (electric current) stimulates to be operated.These Medical Devices (being referred to herein as tissue stimulation prosthese sometimes) usually deliverings Stimulus signal (electric current) compensates the deficiency of recipient.For example, when recipient is passed through due to missing or the destruction of cochlear hair cell When going through sensorineural hearing loss, the histio-irritative hearing prosthesis of such as cochlear implant is often suggested, by acoustics Signal is converted into nerve impulse.Auditory brainstem stimulator is another type of histio-irritative hearing prosthesis, when recipient by It is damaged when sensorineural hearing loss in auditory nerve, may propose auditory brainstem stimulator.

Summary of the invention

In one side proposed in this paper, a kind of implantable medical device is provided.The implantable medical device includes: electric current Source is configurable to generate stimulus signal to be delivered to the recipient of implantable medical device；The array of stimulating electrode；And it is multiple Switch, is configured as each current source in multiple current sources being selectively electrically connected to multiple stimulating electrodes, plurality of Switch is arranged to that adjacent stimulating electrode is prevented to be connected to the identical current source in multiple current sources.

In another aspect proposed in this paper, a kind of tissue stimulation prosthese is provided.The tissue stimulation prosthesis system includes: more A electrode；Multiple current sources；And sparse switching network, be configured as: each current source in current source is connected to one by (i) A above electrode, and each electrode in electrode is connected to the only one subset of current source by (ii).

In another aspect proposed in this paper, a kind of tissue stimulation prosthese is provided.The tissue stimulation prosthesis system includes: more A current source, wherein each current source in current source is configured as generating electrical stimulation signal；The array of stimulating electrode, wherein electricity Pole is configured as that the tissue of recipient will be delivered to from the received electrical stimulation signal of current source；And hardwire electric network, it will be electric Each current source in stream source is connected to the only one subset of electrode.

Detailed description of the invention

It is described in conjunction with the accompanying the embodiment of the present invention herein, in which:

Figure 1A is the schematic diagram for illustrating the cochlear implant according to embodiment proposed in this paper；

Figure 1B is the block diagram of the further details of the cochlear implant of pictorial image 1A；

Fig. 1 C is the schematic diagram of the further details of the cochlear implant of pictorial image 1A；

Fig. 2 is the schematic diagram of the delivering stimulated while diagram according to embodiment proposed in this paper via electrod-array；

Fig. 3 is the schematic diagram for illustrating the stimulator unit with sparse switching network according to embodiment proposed in this paper；

Fig. 4 A, Fig. 4 B, Fig. 4 C, Fig. 4 D and Fig. 4 E are to illustrate to be promoted according to embodiment proposed in this paper by sparse switching network Into the figure of/enabled different example stimulus modalities；

Fig. 5 is the signal for illustrating another stimulator unit with sparse switching network according to embodiment proposed in this paper Figure；

Fig. 6 is the seed type for illustrating a part that can form sparse switching network according to embodiment proposed in this paper Switch schematic diagram；

Fig. 7 is another type for illustrating a part that can form sparse switching network according to embodiment proposed in this paper The schematic diagram of the switch of type；

Fig. 8 is the signal for illustrating another stimulator unit with sparse switching network according to embodiment proposed in this paper Figure；

Fig. 9 is the schematic diagram for illustrating the stimulator unit with sparse switching network according to embodiment proposed in this paper； And

Figure 10 A, Figure 10 B, Figure 10 C and Figure 10 D are to illustrate to be promoted according to embodiment proposed in this paper by sparse switching network Into the figure of/enabled different example stimulus modalities.

Specific embodiment

This paper presents the implantable medical device of such as tissue stimulation prosthese, it is configured as stimulation delivering simultaneously To recipient.In one embodiment, tissue stimulation prosthese includes multiple current sources, multiple electrodes (for example, the linear battle array of electrode Column) and switch hardwire electric network, the hardwire electric network of the switch is herein referred to as " sparse switch net Network ".Sparse switching network is configured as each current source in current source being connected to more than one electrode, and by electrode In each electrode be connected to the only one subset of current source.Sparse switching network is configured as that adjacent electrode is prevented to be connected to Identical current source.

There are many different types of tissue stimulation prostheses, by stimulus signal (electric current) be delivered to recipient (for example, with Compensate the deficiency of recipient).Only for the purposes of explanation, herein with reference to a type of tissue stimulation prosthese (i.e. cochlear implant) Mainly to describe embodiments set forth herein.It should be appreciated that technology proposed in this paper can be with other tissue stimulation prostheses one It rises and uses, including, for example, auditory brainstem stimulator, implantable pacemaker, defibrillator, deep brain stimulation, functional electrostimulation are set Standby, analgesic stimulator, vision prosthesis, other nerves or neuromuscular stimulators etc..

Figure 1A is configured as implementing the schematic diagram of the example cochlea implantation system 100 of the embodiment of the present invention.Cochlea is planted Entering system 100 includes external component 102 and internal/implantable component 104.In this example, can plant component 104 is that cochlea is planted Enter object.Figure 1B is the schematic diagram of a part of cochlear implant 104.

External component 102 is attached directly or indirectly to the body of recipient, and generally includes external coil 106, and And generally include the magnet (in figure 1A do not show) fixed relative to external coil 106.External component 102 further includes for examining At the one or more voice input elements 108 (for example, microphone, electric sound coil etc.) of survey/reception voice signal and sound Manage unit 112.Sound processing unit 112 includes such as power supply (not showing in figure 1A) and Sound Processor Unit (also not in Figure 1A In show).Sound Processor Unit is configured as handling the electric signal generated by voice input element 108, in described embodiment In, voice input element 108 is positioned by the auricle 110 of recipient.Sound Processor Unit (does not show in figure 1A via such as cable Processed signal is supplied to external coil 106 out).

Cochlear implant 104 includes implantable main module (implantation material main body) 114, guidance field 116 and elongated ear Snail internal stimulus component 118.As shown in fig. 1b, main module 114 includes airtight shell 120, is disposed in the shell 120 interior Portion's receiver/transceiver unit 122 (herein referred to as receiver/transceiver circuit device or transceiver unit), And stimulator unit 124.Stimulator unit 124 includes multiple current sources (stimulator) 126 (1) -126 (N), is configured as Stimulus signal (electric current) is generated to be delivered to recipient.As shown, stimulator unit 124 further includes that switch element is (multiple to open Close) hardwire electric network, be referred to herein as " sparse switching network " 125 sometimes.

Such as physical layout/embodiment of the current source of current source 126 (1) -126 (N) is usually in monolithic integrated optical circuit (IC) it completes on to meet the volume needs and power limit of implantation material, and occupies vast resources.Some features of current source It is high-resolution, low-power consumption, high voltage biddability and fast operating.These features need to weigh each other, and need tradeoff pair Current source and the available physical layout area of associated switching device (for example, IC chip area) and/or volume.Modern IC skill A special limiting factor in art is high biddability (such as 5V-20V) the galvanic electrode technology used in system.It can hold Special manufacturing step is needed by the IC device of so high voltage, and device is made physically to become larger.

Transceiver unit 122 is connected to implantable coil 127 (Figure 1B), and in general, magnet (not shown) relative to can Implanted coil 127 is fixed.Magnet and cochlear implant 104 in external component 102 facilitate external coil 106 and implantable line The operation alignment of circle 127.The operation alignment of coil enables implantable coil 127 to receive power and data from external coil 106, And data may be sent to external coil 106.More specifically, in some examples, external coil 106 is via close-coupled Electric signal (for example, power and stimulus data) is transferred to implantable coil 127 by link.Implantable coil 127 is usually conducting wire Aerial coil comprising the sub-thread or multiply platinum or golden conducting wire of multiturn electrical isolation.The electrical isolation of implantable coil 127 is by flexible die (for example, polysiloxanes molding) is made to provide.It should be appreciated that various types of transfer approach can be used, such as infrared (IR), electricity Magnetic, capacitor transmission, inductance transmission etc., are transmitted to cochlear implant from external equipment for power, and in external equipment and ear Data are transmitted between snail implantation material.In this way, Figure 1A and Figure 1B are illustrated only for by power and/or data transmission to cochlea implantation A kind of exemplary arrangement of object 104.

Elongated stimulation component 118 is configured as at least partly being implanted in cochlea 130, and including between multiple longitudinal directions Every intra-cochlear electrode 128.Stimulation component 118 extends through the opening in cochlea 130 (for example, cochlea otomy 132, circle Window 134 etc.), and have and be connected to the proximal end of stimulator unit 124 via sparse switching network 125, and extend through The guidance field 116 of mastoid 119.

Two cochlea external electrodes 140 for being positioned in the outside (outside) of the cochlea of recipient are also shown in figure 1A (1) and 140 (2).Reference leads region 142 including the one or more conducting wires or lead that are embedded in electrically insulating material is by ear Snail external electrode 140 (1) and 140 (2) are electrically connected to sparse switching network 125.As described further below, in certain arrangements In, when via one or more intra-cochlear electrodes 128 (1) -128 (22) deliver stimulated current when, cochlea external electrode 140 (1) and 140 (2) may be used as comparative electrode.Herein sometimes using term " implant electrode " come generally with collectively refer to for cochlea Interior electrode 128 (1) -128 (22) and cochlea external electrode 140 (1) and 140 (2).However, herein sometimes using term " thorn Swash electrode " or " main electrode " Lai Zhidai intra-cochlear electrode 128 (1) -128 (22), with cochlea external electrode 140 (1) and 140 (2) Separation, because intra-cochlear electrode is decided to be near target neural cells (nerve cell to be stimulated).On the contrary, outside cochlea Electrode 140 (1) and 140 (2) are " reference electrodes " for supplementing the operation of stimulation/main electrode (i.e. intra-cochlear electrode).It should be appreciated that Term " stimulating electrode " herein or " main electrode " generally refer to be positioned in target neural cells nearby and as docking The group of the electrode of the cardinal stimuli source operation of receptor, and eliminate the electrode far from target neural cells positioning.

The schematic diagram of more detailed view when the stimulation component 118 that Fig. 1 C is to provide Figure 1A is implanted in cochlea 130.Figure 1C illustrates specific arrangement, and moderate stimulation component 118 includes a electrode 128 in 22 (22), and electrode is marked as in Fig. 1 128 (1) to 128 (22).Electrode 128 (1) -128 (22) forms electrod-array 150.It will be appreciated, however, that reality proposed in this paper Applying example can be implemented with alternative arrangement with different number of electrode.

As shown, electrode 128 (1) is most substrate/proximal end electrode, and electrode equipment 128 (22) is farthest/top Electrode.Electrode 128 (1) -128 (22) be arranged in electrical isolation main body 144 in, electrical isolation main body 144 for example by elastomer or its He forms elastic flexible material.Electrode 128 (1) -128 (22) is all connected to sparse switching network via conducting wire 129 (Figure 1B) 125, conducting wire 129 passes through the main body 144 and lead areas 116 (not showing in Figure 1B or Fig. 1 C) of stimulation component 118.In order to just In explanation, these conducting wires 129 are omitted from Fig. 1 C.Fig. 1 C also illustrates the cochlea dispatch from foreign news agency being positioned in outside recipient's cochlea 142 a part of pole 140 (1) and 140 (2) and reference leads region.

Figure 1B is returned to, main module 114 further includes energy storage device 132 (for example, implantation battery or short-term energy storage electricity Container), power management unit 134, data capture unit 136 and controller (control unit) 138.134 quilt of power management unit It is configured so that energy storage device 132 provides suitable stimulation power (VDD) to stimulator unit 124.As described above, transmitting-receiving Device 122, which is configured such that, can be communicated with the other component of cochlea implantation system 100 (for example, via implantable coil 127).Data capture unit 136 is configured as obtaining data, such as electrode voltage, nerves reaction signal, implantation material health status With diagnostic signal etc..Controller 138 is configured as the operation of various other components of control main module 114.For ease of description, Connection between all parts that main module 114 is omitted in Figure 1B.It is also understood that main module 114 may include other Element, test interface, diagnostic function etc., as the skilled person will appreciate.For ease of description, from It is omitted in Figure 1B and these incoherent various other elements of the disclosure.

As noted, main module 114 further includes stimulator unit 124, as described above, stimulator unit 124 includes more A current source 126 (1) -126 (N) and sparse switching network 125.As it is used herein, " current source " includes one or more Electronic circuit component, delivering (providing (source)) and/or absorption (drawing) electric current.Equally as it is used herein, term " offer " and " drawing " is the term for defining the direction of electric current flowing in the tissue of recipient.As " offer " (i.e. provide/ Deliver electric current) current source the electric current for flowing into the tissue (load) of recipient is provided.As " drawing " (draw/absorb electricity Stream) current source provide from recipient tissue outflow electric current.In this way, term " current source " or " stimulator " should be by broad sense Ground is construed to include that can provide electric current, draw electric current, or can not only provide electric current but also can draw any element of electric current.

As described further below, sparse switching network 125 is configured as in different times selectively by electric current Each current source in source 126 (1) -126 (N) is connected to the only one subset of implant electrode (that is, intra-cochlear electrode 128 (1) - 128 (22) and cochlea external electrode 140 (1) and 140 (2)).That is, as described further below, sparse switching network 125 includes The switch element (switch) of limited/constrained number, is arranged in given time for the current source in stimulator unit 124 In each current source be connected only to a limited number of implant electrode.In certain embodiments, opening in sparse switching network 125 Pass is arranged to that adjacent intra-cochlear electrode is prevented to be connected to identical current source.Alternatively or additionally, sparse switching network 125 can be configured as each current source in current source 126 (1) -126 (N) is connected to more than one in different times Implant electrode.In addition, sparse switching network 125, which can be configured as, is connected to electricity for each implant electrode in implant electrode The only one subset in stream source.

Figure 1A-Fig. 1 C illustrates the arrangement that wherein cochlea implantation system 100 includes external component.It will be appreciated, however, that this The embodiment of invention can with alternative arrangement cochlea implantation system or other prosthesis systems in implement.For example, of the invention Embodiment can also be in completely implantable cochlear implant or another type of completely implantable tissue stimulation prosthese Middle implementation.In completely implantable prosthese, all components are configured to be implanted under skin/tissue of recipient, in this way, Prosthese can operate at least limited period, without external equipment.

It should also be appreciated that Figure 1A, Figure 1B and Fig. 1 C illustrate only certain components of cochlea implantation system 100.In this way, figure The example of 1A, Figure 1B and Fig. 1 C are illustrative, and may include according to the cochlea implantation system of embodiment proposed in this paper The not other assemblies shown in Figure 1A, Figure 1B and Fig. 1 C or element.

Routinely, cochlear implant arouses hearing perception using sequence unipolar stimulation.In sequence unipolar stimulation, cochlea Interior electrode is for providing stimulus signal (electric current), and cochlea external electrode is for drawing stimulus signal.In addition, being once used only one Stimulus signal is delivered to recipient by a electrode, and can use multiple and different electrodes by predetermined order.It passs The cochlear implant of sequence unipolar stimulation is sent usually to utilize a current source, which can be operatively connected to arbitrarily Intra-cochlear electrode, so as to via arbitrary electrode deliver stimulus signal.Another current source can be operatively connected to cochlea External electrode, to draw stimulus signal.

Ideally it is desirable to which stimulus signal only stimulates the narrow zone of the cochlea of recipient (that is, Spiral ganglion neuron Narrow zone) so that the gained neural response from adjacent stimulation channels has least overlapping.However, unipolar stimulation is usual The overlapping for showing height allows target nerve member group by several different monopole channels (that is, in different cochlea The unipolar stimulation delivered at electrode) excitation.Therefore, in order to reduce excitation neural populations size, developed other classes Stimulation strategy of type, including bipolar, three poles, focusing multipole ((FMP), also known as " phased array ") stimulation etc. are logical herein Often and it is collectively known as " focused stimulation strategy " or " focused stimulation ".These stimulation strategies focused generally use certain shape Stimulated while formula, wherein use different amplitude and different polarity (that is, different current directions), substantially simultaneously via Multiple and different electrodes delivers stimulus signal, so as to the electric current being precisely controlled in the tissue of recipient.

Fig. 2 is to illustrate the schematic diagram that focused stimulation is delivered via the stimulation component 118 of Figure 1A-Fig. 1 C.As described above, cochlea Interior electrode 128 (1) -128 (22) includes the linear array 150 being positioned in inside cochlea, and cochlea external electrode 140 (1) It is positioned in outside cochlea with 140 (2).

In the figure 2 example, come using one group of continuous intra-cochlear electrode (i.e. intra-cochlear electrode 128 (4) -128 (8)) same When provide or draw electric current (that is, in different sizes with different polarity/direction delivering electric current), to accurately control tissue In electric current flowing.More specifically, electrode 128 (4) and 128 (8) provide the electric current of (that is, delivering positive polarity electric current) 0.1mA, electricity Pole 128 (5) and 128 (7) provide the electric current of 0.2mA, and electrode 128 (6) draws the electric current of 1mA.In addition, in this example, Additional 0.4mA electric current is also provided using cochlea external electrode 140 (1).In other words, Fig. 2 is illustrated wherein in addition in cochlea The arrangement of additional cochlear electrode (EE1) is also used except electrode (E4-E8).It as described further below, can be by sparse Switching network 125 (Figure 1B) generates focused stimulation shown in Fig. 2, and sparse switching network 125 is configured as in different time Each current source in the current source 126 (1) -126 (N) in stimulator unit 124 is selectively connected to electrode 128 (1) To the only one subset of 128 (22), and/or it is connected to cochlea external electrode 140 (1) and 140 (2).

Relative to unipolar stimulation strategy, all focused stimulations as shown in Figure 2 (and other are stimulated simultaneously, wherein via Multiple intra-cochlear electrodes deliver stimulus signal simultaneously) better stimulated current collection is usually provided at tissue in expected excite In, this may obtain better hearing result in cochlear implant recipient.

In order to obtain the full flexibility on stimulated current profile (that is, how delivering stimulus signal), electricity in each cochlea Pole can have dedicated current source, and dedicated current source control is via the special electrodes (i.e. between current source and intra-cochlear electrode Correspond) delivering electric current.Another selection (can be cut any current source via conventional complete/full switch matrix Change to the matrix of the switch of any electrode) each current source is linked to all electrodes, to realize similar flexibility.

Present inventors have realized that in many stimulation strategies simultaneously, it is not necessary that while via all ears Electrode is stimulated in snail.But inventors have realised that under specific circumstances, a time point, only via in cochlea The a subset of electrode is come while stimulating to be sufficient, therefore, in order to provide the useful system with stimulatory function simultaneously, electric current One-to-one correspondence between source and intra-cochlear electrode is not required.Inventor is also to be recognized that the most useful while stimulation strategy table The electrode mode revealed does not need the complete interconnection between each current source and all electrodes (for example, by conventional full switch square Battle array provides).Therefore, this paper presents the new arrangement for cochlear implant or other tissue irritation's prostheses, enable prosthese It is enough to provide stimulation simultaneously to recipient, but done so using a limited number of current source and switch.

For example, Fig. 3 is 124 (the referred to herein as stimulator of stimulator unit illustrated according to embodiment proposed in this paper Unit 324) one embodiment schematic diagram.In this embodiment, stimulator unit 324 includes six current sources (stimulator) 326 (1) -326 (6) and sparse switching network 325.Sparse switching network 325 is more by what is operated under the control of control unit 360 A switch element (switch) 355 is formed.For ease of description, from the company being omitted in Fig. 3 between switch 355 and controller 360 It connects.Although Fig. 3 illustrates the presence of the controller 360 of a part to form stimulator unit 324, but it is to be understood that this is only It is illustrative, and switch 355 can be by the individual of such as implantation material controller (for example, controller 138 in Figure 1B) Controller is controlled/is activated.

Stimulator unit 324 is shown to have cochlea external electrode 140 (1) and 140 (2) and the electricity of Figure 1A-Fig. 1 C and 2 Pole array 150.Each electrode in intra-cochlear electrode 128 (1) -128 (22) in electrod-array 150 is via corresponding conducting wire 129 (1) -129 (22) are electrically connected to sparse switching network 325.Similarly, cochlea external electrode 140 (1) and 140 (2) respectively via Conducting wire 129 (23) and 129 (24) are connected to sparse switching network 325.

According to embodiment proposed in this paper, sparse switching network 325 is configured as in different times, by current source 326 Each current source in (1) -326 (5) is used to selectively connect to multiple 128 (1) -128 of (that is, more than one) intra-cochlear electrode (22), and by each intra-cochlear electrode in intra-cochlear electrode 128 (1) -128 (22) it is used to selectively connect to current source 326 (1) -326 (5) only one subset.In addition, sparse switching network 325 is configured as current source 326 (6) being selectively connected To cochlea external electrode 140 (1) and/or cochlea external electrode 140 (2).In other words, sparse switching network 325 be include multiple open 355 hardwire electric network is closed, multiple switch 355 is configured as in different times, will be in current source 326 (1) -326 (6) Each current source is used to selectively connect in implant electrode (that is, electrode 128 (1) -128 (22), 140 (1) or 140 (2)) only A subset.Multiple switch 355 is arranged to that adjacent intra-cochlear electrode 128 (1) -128 (22) is prevented to be connected to identical electricity Stream source 326 (1) -326 (5).When being connected to electrode, current source 326 (1) -326 (6) can be provided which or draw electric current.

As shown in Figure 3, each current source in current source 326 (1) -326 (6) is connected to corresponding distributing line 365 (1)-365(6).In certain embodiments, sparse switching network 325 is arranged such that each 128 (1) -128 of intra-cochlear electrode (22) one and the only one distributing line that can be switched in distributing line 365 (1) -365 (5), and cochlea external electrode 140 (1) Distributing line 365 (6) can be all connected to 140 (2).In other words, in certain embodiments, implant electrode (i.e. 128 (1)- 128 (22), 140 (1), 140 (2)) in each implant electrode there is single associated switch in sparse switching network 325 355, one and only one current source corresponding electrode being selectively electrically connected in current source 326 (1) -326 (6) (or disconnect corresponding electrode with it and be electrically connected).

As shown, there are five 326 (1) -326 of current source that may be coupled to intra-cochlear electrode 128 (1) -128 (22) (5), and it may be coupled to the 6th current source 326 (6) of cochlea external electrode 140 (1) and 140 (2).Therefore, in the example of Fig. 3 In, sparse switching network 325 be further configured such that every five intra-cochlear electrodes may be coupled to identical distributing line 365 (1), 365 (2), 365 (3), 365 (4) or 365 (5), and be therefore connected to identical current source 326 (1), 326 (2), 326 (3), 326 (4) or 326 (5).In more general terms, in the presence of " M " a current source that may be connected to intra-cochlear electrode 128 (1) -128 (22), And sparse switching network 325 is configured as every M intra-cochlear electrode being connected to identical distributing line, and is therefore connected to Identical current source.

M current source enables stimulator unit according to many different stimulations from the connection of every M intra-cochlear electrode Electric current is delivered to recipient by mode.For example, Fig. 4 A- Fig. 4 E is to illustrate to be promoted/enabled by the sparse switching network 325 of Fig. 3 The figure of different example stimulus modalities.In the example of Fig. 4 A- Fig. 4 E, current source 326 (1), 326 (2), 326 (3), 326 (4), 326 (5) and 326 (6) are indicated by label S1, S2, S3, S4, S5 and S6 respectively.Similarly, intra-cochlear electrode 128 (1), 128 (2), 128 (3) etc. are indicated by corresponding label E 1, E2, E3 etc., and cochlea external electrode 140 (1) and 140 (2) are respectively by label EE1 and EE2 is indicated.

In general, sparse switching network 325 can be (in cochlea electric via any M (i.e. 5) or less sequence stimulation point Pole) stimulus signal (for example, providing and/or draw electric current) is provided and/or draws simultaneously, have zero to three between continued stimulus point A dispersing electrode.For example, Fig. 4 A illustrates an example, wherein via five continuous electrodes (that is, between each stimulation point There is no dispersing electrode) stimulation is simultaneously provided/draws, wherein also providing or drawing electric current in cochlea external electrode.Fig. 4 B and Fig. 4 C Each illustrate example, wherein via be respectively separated from each other by a dispersing electrode multiple electrodes (that is, each stimulation point it Between there are a dispersing electrodes) simultaneously provide/draw stimulation, wherein also providing in cochlea external electrode or drawing electric current.Fig. 4 B It is with the exemplary place different from each other of Fig. 4 C, provided in each example using different electrodes/draw electric current.Accordingly Ground, Fig. 4 B and Fig. 4 C illustrate the i-coch different stimulated position of recipient.

Fig. 4 D illustrates an example, wherein via two dispersing electrodes are passed through (that is, there are two nothings between each stimulation point Effect electrode) and the multiple electrodes that are separated from each other and are not provided or are drawn at cochlea external electrode simultaneously to provide/draw stimulation Obtaining current.Fig. 4 E illustrates an example, wherein via three dispersing electrodes are passed through (that is, there are three between each stimulation point Dispersing electrode) and the multiple electrodes that are separated from each other simultaneously provide/draw stimulation, wherein also providing or drawing in cochlea external electrode Electric current.

As described above, stimulus modality shown in Fig. 4 A- Fig. 4 E is illustrative, and other stimulus modalities are also possible 's.In some arrangements, stimulus modality can be depending on the value (that is, the number that may be connected to the current source contacted in cochlea) of M. For example, can be enabled to according to the sparse switching network of embodiment proposed in this paper continuous at 2M-1 if M is odd number It is stimulated at each second electrode of electrode.If M is odd number prime number, sparse switching network allows continuous at KM-X+1 M enterprising assassinate in electrode are swashed, and have X-1 dispersing electrode between each stimulation point, wherein X is natural number.

Fig. 3 and Fig. 4 A- Fig. 4 E generally illustrates in wherein stimulator unit that there are the arrangements of M+1 current source, wherein " M " a current source can be operatively connected to intra-cochlear electrode, and additional current source (that is, 1 current source of "+") may be selected It is connected to cochlea external electrode to property.Fig. 5 be illustrate by using M+2 current source provide one of increased flexibility it is standby Select the schematic diagram of embodiment.

More specifically, Fig. 5 illustrates one embodiment (referred to herein as stimulator unit of stimulator unit 124 524) comprising seven current sources 526 (1) -526 (7) and sparse switching network 525.Sparse switching network 525 is by multiple switch The formation of element (switch) 555, switch element (switch) 555 operate under the control of control unit (controller) 560.Similar to figure 3 arrangement from the connection being omitted between switch 555 and controller 560 in Fig. 5, and should manage for ease of description Solution there are controller 560 is illustrative (that is, switch 555 can be by such as implantation material controller in stimulator unit 524 Individual controller control/activate).

Stimulator unit 524 is shown to have the electricity of cochlea external electrode 140 (1) and 140 (2) and Figure 1A-Fig. 1 C and Fig. 2 Pole array 150.The intra-cochlear electrode 128 (1) -128 (22) of electrod-array 150 is via corresponding conducting wire 129 (1) -129 (22) electricity It is connected to sparse switching network 525.Similarly, cochlea external electrode 140 (1) and 140 (2) are respectively via conducting wire 129 (23) and 129 (24) it is connected to sparse switching network 525.

According to embodiment proposed in this paper, sparse switching network 525 is configured as in different times, by current source 526 Each current source in (1) -526 (5) is used to selectively connect to multiple 128 (1) -128 of (that is, more than one) intra-cochlear electrode (22), and by each intra-cochlear electrode in intra-cochlear electrode 128 (1) -128 (22) it is connected to 526 (1) -526 of current source (5) only one subset.In addition, sparse switching network 525 is configured as current source 526 (1) being used to selectively connect to cochlea External electrode 140 (1) and/or cochlea external electrode 140 (2).In other words, sparse switching network 525 is by current source 526 (1)- Each current source in 526 (6) is connected to implant electrode (that is, electrode 128 (1) -128 (22), 140 (1) or 140 (2)) only The hardwire electric network of a subset.Multiple switch 555 is arranged to prevent adjacent intra-cochlear electrode 128 (1) -128 (22) It is connected to identical current source 526 (1) -526 (5).

As shown in Figure 5, each current source in current source 526 (1) -526 (6) is connected to corresponding distributing line 565 (1)-565(6).In certain embodiments, sparse switching network 525 is arranged such that each 128 (1) -128 of intra-cochlear electrode (22) it may be coupled to one in distributing line 565 (1) -565 (5) and only one distributing line, and cochlea external electrode 140 (1) Distributing line 565 (6) can be all connected to 140 (2).In other words, in certain embodiments, implant electrode (i.e. electrode 128 (1) -128 (22), 140 (1) and 140 (2)) in each implant electrode associated in sparse switching network 525 open 555 are closed, which is selectively electrically connected to corresponding electrode one in current source 526 (1) -526 (6) A and only one current source (or corresponding electrode is made to disconnect electrical connection).

As noted, stimulator unit 524 further includes that the 7th current source 526 (7) (herein referred to as assists Current source), arbitrary implant electrode is connected to the property of can choose (that is, electrode 128 (1) -128 (22), 140 (1) or 140 (2)).More specifically, sparse switching network 525 includes the 7th distributing line 565 (7) (herein referred to as supplement or auxiliary Help distributing line), each implant electrode in implant electrode may be electrically connected to the 7th distributing line.In other words, implant electrode The associated main switch 555 of each implant electrode in (i.e. electrode 128 (1) -128 (22), 140 (1) and 140 (2)) with And electrode is electrically connected to current source 526 (1)-by the associated auxiliary switch 555 in sparse switching network 525, main switch 555 Corresponding electrode is selectively electrically connected to auxiliary distributing line 565 (7) by a current source in 526 (6), auxiliary switch 555 And therefore current source 526 (7) (or corresponding electrode is made to disconnect electrical connection).

In the arrangement of Fig. 5, current source 526 (1) -526 (6) referred to herein as " master " current source, and it is as noted , current source 526 (7) sometimes referred to as " assists " current source.Multiple switch 555 in sparse switching network 525 is arranged to The only one master each implant electrode in multiple implant electrodes being used to selectively connect in master current source 526 (1) -526 (6) Current source, and all implant electrodes are used to selectively connect to auxiliary current source 526 (7).

In short, the sparse switching network 525 of Fig. 5 includes and implant electrode 128 (1) -128 (22), 140 (1) and 140 (2) In associated two switches 555 of each implant electrode.First switch in two switches 555 associated with electrode makes One in master current source 526 (1) -526 (6) and only one master current source can be used to selectively connect to by obtaining corresponding electrode, And with second switch in associated two switches 555 of electrode so that corresponding electrode is only selectively connected to auxiliary electricity Stream source 526 (7).Arbitrary electrode 128 (1) -128 (22), 140 (1) and 140 (2) are connected to auxiliary current source 526 (7) ratio Arrangement shown in Fig. 3 increases stimulation flexibility.

Above embodiments are described by reference to the sparse switching network for including " switch element " or " switch ".Such as this paper institute It using, term " switch element " and " switch ", which should be interpreted broadly to embrace, can be controlled to selectively create/ Formation and any element of termination/disconnection electrical connection.For example, as it is used herein, term " switch element " and " switch " are answered When being interpreted as including, Low ESR float switch, high side/downside (dual path) switchs and other circuit elements.

Fig. 6 is the schematic diagram for illustrating example float switch 655, which can form according to mentioning herein A part of the sparse switching network of embodiment out.As shown, example float switch 655 is by a thick-oxide gold in two (2) Belong to oxide semiconductor field effect transistor (MOSFET) 657 (1) and 657 (2) are formed, one as sparse switching network Divide and current source 626 is used to selectively connect to electrode 629.

Fig. 7 is diagram example high side/low side switch 755 schematic diagram, which can form According to a part of the sparse switching network of embodiment proposed in this paper.As shown, example high side/low side switch 755 is by two The MOSFET 659 (1) of a drain extended and 659 (2) are formed, and as a part of sparse switching network, being configured as will be electric Stream source 726 is used to selectively connect to electrode 729.Fig. 7, which is illustrated, provides and draws the arrangement in electric current via individual conducting wire.Cause This, in this embodiment, when via electrode 729 provide electric current when, MOSFET 759 (1) be closed (conducting), and electric current edge by The flowing of direction shown in arrow 762.When drawing electric current via electrode 729, MOSFET 759 (2) is closed (conducting) and electric current It is flowed along the direction as shown in arrow 764.That is, in Fig. 7, the first side of switch 755 is for delivering electric current, and switch 755 Second side is for drawing electric current.It may be advantageous using high side/low side switch 755 (sometimes referred to as dual path switch), because Less IC area is consumed for the on-off ratio such as float switch of these types.

It should be appreciated that the example of Fig. 6 and Fig. 7 is merely illustrative, other kinds of switch/switching element can also with or it is standby Selection of land is used in sparse switching network proposed in this paper.It should also be appreciated by one skilled in the art that above description describes bases The core architecture of the sparse switching network of the embodiment of the present invention, and other modifications are also within the scope of the invention.For example, dilute The each electrode points dredged in switching network can have extra switch, for connecting measuring device or carrying out post-stimulatory electrode Short circuit.It is also understood that each stimulator can have two physical distribution line/conducting wires (one for drawing electric current, one with In offer electric current), allow to avoid using Low ESR float switch.This arrangement is described below with reference to Fig. 8.

Fig. 8 illustrates one embodiment (referred to herein as stimulator unit 724) of stimulator unit 124, benefit With element shown in Fig. 7.For ease of description, stimulator unit 724 is shown to have cochlea external electrode 140 (1) and 140 (2) and the electrod-array 150 of Figure 1A-Fig. 1 C and Fig. 2.

As shown, stimulator unit 724 includes six current sources 726 (1) -726 (6) and sparse switching network 725.It is dilute Switching network 725 is dredged to be formed by multiple high side/low side switch 755 (as shown in Figure 7) and a plurality of distributing line 765.Current source 726 Each current source in (1) -726 (6) is arranged such that electric current via the different distributing lines 765 of sparse switching network 725 And it is provided and draws (that is, each current source 726 (1) -726 (6) has two physical distributions line/conducting wire associated there 765, one is used to draw electric current, and another for providing electric current).It is connected to two of identical current source 726 (1) -726 (6) Distributing line 765 can be used to selectively connect to electrode via identical high side/low side switch 755.For example, as shown in Figure 8, Two distributing lines 765 associated with 726 (1) can be connected to electrode 128 (1) via single high side/low side switch 755 (that is, being connected to conducting wire 129 (1)).This two distributing lines 765 associated with 726 (1) can also be via other single high Side/low side switch 755 is connected to other electrodes (for example, electrode 128 (6), 128 (11), 128 (16) and 128 (21))

In general, high side/low side switch 755 is under the control of the control unit of (controller) 760, implant controller etc. Operation, in different times, each current source in current source 726 (1) -726 (5) is selectively connected multiple (i.e. one More than a) intra-cochlear electrode 128 (1) -128 (22), and will be in each cochlea in intra-cochlear electrode 128 (1) -128 (22) Electrode is connected to the only one subset of current source 726 (1) -726 (5).In addition, sparse switching network 725 is configured as electric current Source 726 (6) is used to selectively connect to cochlea external electrode 140 (1) and/or cochlea external electrode 140 (2).In other words, sparse switch Network 525 is that each current source in current source 726 (1) -726 (6) is connected to implant electrode (that is, 128 (1) -128 of electrode (22), 140 (1) or 140 (2)) only one subset hardwire electric network.Multiple switch 555 is arranged to prevent adjacent Intra-cochlear electrode 128 (1) -128 (22) is connected to identical current source 726 (1) -726 (1).When being connected to electrode, current source 726 (1) -726 (6) can provide or draw electric current via a distributing line in two associated distributing lines 765 respectively.

The design of stimulation apparatus is usually the (example driven by providing the demand of maximum flexibility in available stimulation strategy Such as, it is all stimulated under any circumstance via all electrodes).Embodiment proposed in this paper and these common design alternatives It is uncorrelated.Particularly, embodiment proposed in this paper intentionally reduces stimulation flexibility, to reduce hardware size/cost.Pass through The number and the size of limit switch network simultaneously of current source are limited, embodiment proposed in this paper, which provides, hardware resource Effect uses, to realize while stimulate ability.As a result, relative to the conventional IC based on one-to-one framework, technology proposed in this paper makes Function simultaneously can still be provided with reduced size design IC (the implantation material volume for being converted to reduction) by obtaining.In addition, Technology proposed in this paper can reduce implantation material power requirement by reducing the number of current source and/or switch.

Figure 1A-Fig. 8 generally illustrates the use of sparse switching network Yu one-dimensional (linear) electrod-array.It should be appreciated that The sparse switching network of embodiment according to the present invention can also be used together with two-dimensional array of electrodes.Two-dimensional array of electrodes can be with For such as brain stem stimulator, eyesight prosthese etc..

In the sparse switching network being used together with two-dimensional array of electrodes, stimulator unit includes being arranged as " K " group Multiple stimulators of (that is, the 1st, 2,3...K group).It all includes " M that " K ", which organizes each of stimulator,_k" a stimulator, wherein " k " is the integer from 1 to K.Different K group stimulators may include stimulator (the i.e. M of identical or different number_kIt can be equal to Or M can be not equal to).As described further below, the sparse switching network being used together with two-dimensional array of electrodes is configured To enable every group of stimulator to service every K row electrode in a manner of identical with one-dimensional array.

Two-dimensional array of electrodes includes " J " row electrode.Every row in these " J " row includes " N_j" a electrode, wherein j is from 1 To the integer of J.Equally, it is not necessary to which all rows of electrodes all have equal number of electrode, but N can be set_j=N.In order to suitable Hardware is saved in locality, it is assumed that the electrode number in every row is greater than number (the i.e. N of the stimulator for the row service_j>M_kOr possibly N_j>>M_k), and the number of row is greater than the number (that is, J > K or possibly J > > K) of stimulator group.

Fig. 9 is the schematic diagram for illustrating the stimulator unit 924 according to embodiment proposed in this paper, and stimulator unit 924 wraps Include a stimulator 926 (1) -926 (10) in ten (10) and sparse switching network 925.Sparse switching network 925 is configured as to stimulate Device 926 (1) -926 (10) is used to selectively connect to two-dimensional array of electrodes 950.

Sparse switching network 925 (is opened by the multiple switch element operated under the control of control unit (controller) 960 Close) 955 formation.For ease of description, from the connection having been had been left out in Fig. 9 between switch 955 and controller 960.Although Fig. 9 Illustrating the presence of the controller 960 of a part to form stimulator unit 924, but it is to be understood that this is merely illustrative, And switch 955 can be by individual controller control/actuating.

In this example, electrod-array 950 includes a electrode 928 (1) -928 (90) in 90 (90), is organized into and wraps Include multiple and different row/teams 931 (1) -931 (9) of 10 electrodes.Also shown in Fig. 9 two reference electrodes 940 (1) and 940(2).In the example of figure 9, there are three groups of stimulators (that is, K=3), referred to as 985 (1) of group, 985 (2) and 985 (3).This Each of three groups include three stimulators (that is, M_k=3 and M_k=M).As noted, there are nine row electrodes 931 (1)- 939 (9) (that is, J=9), wherein each row include 10 electrodes (that is, N_J=10 and N_J=N).There is also for two reference electrodes 940 (1) and 940 (2) service additional stimulator 926 (1).

According to embodiment proposed in this paper, sparse switching network 925 is configured as in different times, by current source 926 Each current source in (1) -926 (9) is used to selectively connect to multiple (that is, more than one) electrodes 928 (1) -928 (90), and And each electrode in electrode 928 (1) -928 (90) is used to selectively connect to only one of current source 926 (1) -926 (9) Collection.In addition, sparse switching network 925 be configured as current source 926 (10) being used to selectively connect to reference electrode 940 (1) and/ Or reference electrode 940 (2).In other words, sparse switching network 925 is the hardwire electric network for including multiple switch 955, this is more A switch 955 is configured as being selectively connected each current source in current source 926 (1) -926 (10) in different time To the only one subset of implant electrode (that is, electrode 928 (1) -928 (90), 940 (1) or 940 (2)).

More specifically, in the example of figure 9, sparse switching network 925 is configured such that each group 985 of stimulator (1), 985 (2) and 985 (3) can service every three rows electrode in a manner of identical with one-dimensional array.For example, stimulator 926 (1), 926 (2) and 926 (3) form stimulator group 985 (1), and stimulator 926 (4), 926 (5) and 926 (6) form stimulator group 985 (2), and stimulator 926 (7), 926 (8) and 926 (9) form stimulator group 985 (3).Sparse switching network 925 is matched It is set to so that be connected to the electrode in row 931 (1), 931 (4) and 931 (7) with organizing the stimulator property of can choose in 985 (1), And it is connected to the electrode in row 931 (2), 931 (5) and 931 (8) with organizing the stimulator property of can choose in 985 (2) (that is, every three Row electrode).The electrode being connected to organizing the stimulator property of can choose in 985 (3) in row 931 (3), 931 (6) and 931 (9).

The sparse switching network 925 of Fig. 9 makes it possible to deliver electric current to recipient according to many different stimulus modalities.Example Such as, Figure 10 A- Figure 10 D is the figure for illustrating the different example stimulus modalities for being promoted/being enabled by the sparse switching network 925 of Fig. 9.In In the example of Figure 10 A- Figure 10 D, current source 926 (1), 926 (2), 926 (3), 926 (4), 926 (5), 926 (6), 926 (7), 926 (8), 926 (9)) and 926 (10) respectively by label S1, S2, S3, S4, S5, S6, S7, S8, S9 and S10 indicate.Similarly, Electrode 928 (1), 928 (2), 928 (3) etc. are indicated by corresponding label E 1, E2, E3 etc., and reference electrode 940 (1) and 940 (2) it is indicated respectively by label E E1 and EE2.

In general, the example of Figure 10 A- Figure 10 D has the possibility similar with one-dimensional array when checking individual row Property.Every row in row 931 (1) -939 (9) can be serviced with mode identical with the electrode in one-dimensional array (for example, appointing The continuous rows of the K of anticipating, to 2K+1 row, every two row, etc.).But as shown, because stimulator in a group need not Identical row is all served, so increasing additional flexibility.

For ease of description, Fig. 9 illustrates rectangle two-dimensional array 950.It should be appreciated that according to embodiment proposed in this paper Rarefication stimuli network can also be used together with the two-dimensional array (for example, square, hexagonal array etc.) with other shapes, And the use of rectangle two-dimensional array is illustrative.

Only for the purposes of explanation, mainly to describe herein with reference to a type of tissue stimulation prosthese (i.e. cochlear implant) The embodiment of proposition.It will be appreciated, however, that technology proposed in this paper can be used together with other tissue stimulation prostheses, including, For example, auditory brainstem stimulator, implantable pacemaker, defibrillator, functional electrostimulation equipment, analgesic stimulator, vision prosthesis, Other nerves or neuromuscular stimulators etc..

It should be appreciated that above-described embodiment did not excluded each other, and can be combined with each other with various arrangements.

The range of described and claimed herein is not limited by certain preferred embodiment disclosed herein, because These embodiments are intended as explanation, rather than limit several aspects of the invention.Any equivalent embodiment is intended at this In the range of invention.In fact, according to foregoing description, of the invention is various other than those of shown and described herein Modification will become obvious those skilled in the art.This modification, which is also intended to, falls within scope of the appended claims It is interior.