Targeting device for an implant

Abstract

A method of securing an implant into a bone using a targeting device having at least two magnetic field communication units are disclosed. The device consists of at least a receiver and transmitter for multi-axis pulsed direct current magnetic signals in each of three orthogonal planes. One of the communication units carried in a fixed position by a drill guide and a second of the communication units is in a fixed, offset position relative to an implant connector. The position and orientation of the drill guide relative to the implant connector is determined by the transmission of the pulsed direct current magnetic signal from the transmitting unit and receiving that signal at the receiver. The signals provide the position and location of the communication units in relation to one another. The signals are converted into position and orientation data format readable by a programmed computer. The converted data is displayed on the display, enabling the alignment of the drill guide with the connector by viewing the virtual representation of the position and orientation of the connector and drill guide. A substantially offset support member can be used to releasably support the proximal end of the implant. A third communication unit in the support member can also communicate with the unit in the drill guide to enable the calculation of the relative locations of connector and drill guide.

Description

FIELD OF INVENTION

The invention relates to the positioning of a first element, relative to a second device, through the use of direct current magnetic field generating and receiving devices, and more particularly, to the installation of orthopaedic implants. More particular, it relates to an improvement over existing devices used for locating holes in an implanted prosthesis so that a screw or pin for interlocking the prosthesis either with itself or with the surrounding bone can be accurately installed. The invention specifically relates to a positioner or aiming (targeting) device for locking screw or pins for such orthopedic hardware which employs pulsed direct current (DC) transmitted signals to enable precise positioning of such screws or pins.

BACKGROUND OF THE INVENTION

Various intramedullary nails and targeting devices for interlocking the intramedullary nail to the surrounding bone, particularly for the use in repairing the femur, are known in the prior art. One targeting method that is capable of providing precise locating of the holes distally uses x-ray techniques, but long periods of x-ray exposure are required and the need to move the x-ray equipment in and out of position to check the screw or pin locations means that there is a risk of a loss of alignment each time the equipment is moved. Patents of interest in this field include U.S. Pat. Nos. 5,537,453 (Williams et.al.); 5,478,343 (Ritter); 5,426,687 (Goodall et al); 5,178,621 (Cook, et. al.); 5,031,203 (Trecha); 5,030,222 (Calandruccio et al); 5,013,317 (Cole et al); and others as cited in the above patents. As a consequence of these radiographic techniques, the positioning of such locking screws or pins is typically the most time consuming and difficult portion of the overall rod implantation procedure.

Two other patents are thought to be of more general interest, U.S. Pat. Nos. 4,625,718 (Olerud et al.), and 4,570,624 (Wu). The Olerud et al. patent disclosing an aiming apparatus using X-ray techniques for making holes or bores in the bone of a patient in registration with the holes or bores on an interlocking nail, and the Wu patent disclosing a mechanical technique for aligning surgical pins in parallel.

Patents of interest in this field include U.S. Pat. Nos. 4,621,628 (Brudermann); 5,049,151 (Durham et al); and 5,514,145 (Durham et al). The Brudermann patent discloses an apparatus for locating transverse holes in the distal end of implanted locking nails. The apparatus includes at least one magnet which generates an axially symmetrical field, in combination with a magnetic field detecting device or sensor having an axial field reception characteristic. In one embodiment, the magnetic field sensor is inserted into an implanted nail and the magnet, which is placed on the surface of the skin, is moved until axes of the magnetic field of the magnet and the sensor are aligned. More particularly, the sensor is connected to an external display device and alignment of the respective magnetic fields is indicated when a zero-point indication is provided on the display device. A second magnet can be used to increase the precision of the alignment process. The directional characteristics of the magnetic field detection device are used to control the relative positions of the axes of both directional elements through a display device, such that both axes are brought into congruence with each other by means of the control display. When one of the directional elements is aligned exactly with the axis of the of the transverse hole in the in the nail, another element can be used externally to mark the location of the nail hole for positioning of a drilling jig.

The two patents by Durham et al. relate to a method and apparatus for positioning the screws or pins of orthopedic hardware devices such as intramedullary rods which involves the positioning of a first magnet at the location of a screw hole in the nail and then using an aiming device, comprising a second magnet which interacts with the first magnet, to locate the first magnet and hence enable a screw or pin to be placed in the screw hole in the nail to lock the nail in position.

In one first embodiment, an insertion rod is used to position the first magnet at the level of the hole in the rod while in another embodiment, a solid nail is used and the magnet is removable disposed within the hole in the nail prior to implantation of the nail.

One serious disadvantage common to the magnetic field detection devices is the detrimental influence of stray magnetic fields, such as, for example the earth magnetic field, or the effect of field distortion due to highly conductive materials in the form of aluminum, titanium, stainless steel and copper used in the construction of operating room tables and surgical implants. The art of using transmitting and receiving components with electromagnetic coupling for measuring position and orientation is well known especially with respect to armament sighting systems where the receiver component would be located in a gunner's helmet and a transmitter component would be attached to a nearby electrically non-conductive structure. As the gunner would sight-in a target through a sighting cross-hair affixed to his helmet, the receiver located thereupon would pick up signals generated by the transmitter. These signals would then be processed by a computer to determine the position and orientation of the helmet and then to contemporaneously point a unit of armament in the same direction as the helmet mounted sight piece. As taught in U.S. Pat. No. 4,054,881 (Raab) and U.S. Pat. No. 4,287,809 (Egli et al.), and U.S. Pat. No. 4,314,251 (Raab) and U.S. Pat. No. 4,396,885 (Constant), an alternating current (AC) signal is applied in a time division or frequency division format to a transmitter consisting of two or three orthogonal coils which generate an AC electromagnetic field which is measured by an AC receiver likewise consisting of three or two orthogonal coils. These sensed signals are then filtered and amplified in a method compatible with the transmitted format, converted to a digital format and then read into a computer where various mathematical methods are resorted to in order to extract position and orientation with resort to applicable electromagnetic field equations.

All current systems such as the ones above, that utilize an AC transmitted signal work accurately only when there are no electrically conductive materials located near either the transmitter or receiver because any transmitted AC signal would invariably induce eddy currents in these conductive materials which would in turn serve to generate an AC magnetic field that would distort any transmitted field, and, of course, any ultimate output position and orientation data. In fighter aircraft or helicopters where it is desired to use these position and orientation measuring systems, there are a lot of highly conductive materials in the form of aluminum, titanium, magnesium, stainless steel, and copper used in the construction of the cockpit structure, seat, wiring and helmet-mounted displays. U.S. Pat. No. 4,287,809 teaches a method of compensating for the errors resulting from any field distortion due to cockpit metal that does not move with respect to the transmitter. The compensation method therein suggested involves making measurements throughout the cockpit to determine the amount of such distortion and then using this data to form a correction that is applied to the sensed signals. In a similar manner, U.S. Pat. Nos. 4,394,831 (Egli et al.) and 4,621,628 (Brudermann) teaches a method to accomplish compensation for errors due to eddy currents induced in metal such as would be found in a display located on a pilot's helmet or operating ing field, respectively. This compensation method again requires initial experimental measurements of such distortion in order to effect necessary corrections and provides moderate improvements in accuracy only when the amount of metal is concentrated in a single location and the transmitter does not go through large angular rotations or translations. These types of compensation efforts that are required to make AC systems work accurately are time consuming and expensive to perform and only work in environments where there would not be too much conductive material near transmitter or receiver units. In many locations, for example, AC systems cannot be utilized at all because the distortions produced are simply too large to be corrected merely by such mapping.

It is the object of this invention to provide an effective and economical device for the determination of the location and orientation of the holes in orthopaedic implants. Still another object of the present invention is to provide a targeting device which can be utilized by the majority of current intramedullary nails currently available to the surgeon.

SUMMARY OF THE INVENTION

The invention includes a two- or three-axis transmitter positioner driven by a pulsed DC current, external to the patient, coupled with three- or two-axis receivers positioned internal and/or external to the implant. The receivers are sensitive to a transmitted DC magnetic field emanating from the activated transmitter. Receiver signal processing electronics control the receiver and serve to convert its output to a format suitable for processing by a digital computer in conjunction with a method for processing received signals so as to thereby develop position and orientation data of the transverse locking holes or pin placement. Such data then can be graphically displayed to the user so as to guide the user for accurate alignment of a drill bit with the transverse holes in the implanted device.

The devices presented in U.S. Pat. Nos. 4,945,305 and 4,849,692 (Blood) represents a radical departure from all of the prior art relating to such transmitting and receiving position and orientation devices, insomuch as it avoids, in-toto, resort to AC signals and instead relies upon direct current (DC) signals. Such reliance on DC signals obviates completely any need for a priori calibration undertakings and greatly expands the potential utility of devices of this type. Moreover, manufacture and utilization of this device for purposes of accomplishing all that current devices can accomplish is manifestly less expensive than such manufacture and utilization of said currently used devices are or potentially will be.

It has now been found that the use of the devices of U.S. Pat. Nos. 4,945,305 and 4,849,692, the disclosure of which are incorporated by reference herein, as though recited in full, can be applied to the installation of orthopaedic implants and, more particularly, to the locating of holes in an implanted prosthesis so that a screw or pin for interlocking the prosthesis either with itself or with the surrounding bone can be accurately installed, with surprising effective results.

The invention provides a system of transmitting and receiving antennae that by themselves intrinsically and with inherent electronic means together with a digital computer readily measure position and orientation relative to one another without the need for expensive calibration procedures undertaken in advance of implementation and further without concern for what types of diamagnetic or paramagnetic metallic materials are nearby. For the first time, for instance, devices of this nature can be used in surgical procedures in conjunction with metallic implants and surgical apparatus.

The invention provides for the determination of the displacement vector and determination of the orientation of the orthogonal axis of the receiver relative to the transmitter, FIG. 1. The transmitter is considered the origin of an orthogonal coordinate system of x, y, and z coordinates wherein the z-axis is considered, generally, in line with the gravitational axis of the earth, the x and y axes then lie in the horizontal plane, perpendicular to the z axis and according to a Cartesian coordinate system. The Cartesian system consists of three mutually perpendicular lines or axes that intersect at a common point such that the location of a point relative to the origin can be determined without ambiguity. In addition, each receiver establishes a reference coordinate system with respect to the respective receiver and relative to the transmitter origin such that the location of the receiver can be determined from the transmitter, as well as the rotation of each axis of the receiver system relative to the transmitter.

It is an advantage of the invention that the coordinate reference system of the receiver can be electronically offset to a desired location using the inherent electronic means together with a digital computer. As shown in FIG. 6, the reference axis Si of receiver 107 at location r1 can be electronically offset to a location r1' with a reference axis S1' such that the location vector and the angular orientation of the axis S1' from the transmitter can be ascertained. Likewise, the receiver axis of each receiver can be offset to any desired positioned.

It is a further advantage of the invention that the relative position and orientation between two or more offset locations can be ascertained using the inherent electronic means together with a digital computer.

It is a further advantage that the relative distance between two or more offset axes can be minimized such that one or more of the relative components of the relative displacement vector be minimized and the corresponding axes aligned in space.

The invention provides a distinctly less expensive sighting device than is currently provided within the framework of the present state of the art separate and apart from the cost savings to be realized from abrogation of calibration requirements. Presently, the cores of the transmitting components of these devices are made up of Ferrite. Ferrite is rather expensive, but, in addition to this, it is also rather fragile and difficult to shape. However, Ferrite is necessary as a core piece the prior art device in order to keep eddy current distortion acceptably low where AC current is used. But, there are no AC signal components in the instant device's steady state signal and hence, the same magnetic flux concentration as can be had with Ferrite can likewise be had and used with this device by resorting to less expensive iron or steel for a transmitting core piece, since, with this device, there is no need to be concerned with eddy currents at all.

The instant invention provides a targeting apparatus which does not require the use of radiographic radiation in determining the location of the transverse holes of intramedullary implants, particularly of the distal holes of interlocking nail. The apparatus of the present invention provides, fast, convenient and secure placement of the drilling jig in axial alignment with the transverse holes without involving the radiation exposure on the surgeon, patient, and other medical personnel. The current surgical practice in the use of the image intensifier to locate the unseen transverse holes in the implant and to target the hole for drilling and placement of interlocking screws exposes the surgeon to excessive amounts of radiation during the course of the procedure.

Another advantage of the present invention is that it provides a targeting device which can be utilized by the majority of current intramedullary nails currently available to the surgeon. The current mechanical locating devices are usually implant specific and require the use of the image intensifier to locate the orientation of the distal locking holes. The Distal Targeting Device described in the Russell-Taylor Surgical Technique brochure (Smith & Nephew Richards, Memphis Tenn.) is a "bomb site" apparatus which is mechanically fastened to the proximal end of the nail and utilizes the image intensifier to locate and drill the necessary holes. The mechanical targeting system described in U.S. Pat. No. 4,913,137 is specific to that device. The targeting mechanism described by Azer et al requires that the described nail have a bifurcated tip, a cross section complimentary to other instrumentation, and a mechanism for attachment to the proximal end of the nail. The rod mounted targeting mechanism described in the surgical technique for the Alta Trauma System by Howmedica (Rutherford, N.J.) requires the initial location of the distal holes, the attachment of the targeting assembly mechanism to the nail, and further fluoroscopic control to position the targeting assembly over the distal holes. Another technique used for the above systems, as well as all the other nail systems, requires the use of direct fluoroscopic imaging to locate and align the holes with out any mechanical or electrical connections is called "free handing". This technique is described in detail in the brochures by Smith & Nephew Richards, Zimmer (Warsaw, Ind.), Ace Medical (Los Angeles, Calif.) and Biomet (Warsaw, Ind.).

The described technique and devices of the present invention can be customized for any of the described intramedullary nails.

In accordance with the invention, a DC coupled electromagnetic sensor is provided which is easier to use than prior art devices and which provides easier and more accurate alignment than is afforded by the prior art. In this regard, although the positioner arrangement of the Brudermann and Durham et al. patents discussed above possesses a number of important advantages over the radiographic locator devices, the present invention provides important additional advantages over the positioner arrangement disclosed in those patents, particularly in the areas of ease of use and ease and quality of the alignment.

In one aspect of the invention, a DC coupled electromagnetic positioning system is provided for assisting in positioning a fastening element at a desired concealed internal location such as at a locking screw hole in an intramedullary rod in the bone of a patient, the arrangement comprising: a pulsed DC current transmitter, a first receiver, or a plurality of receivers, that is sensitive to the transmitted DC magnetic field adapted to be positioned at said internal location and providing a two or three axis directional reference or coupled with the implant at a known offset location and orientation from the internal location to be positioned; and a second or additional receivers thus providing multiple reference positioning devices external to the patient; the positioning device comprising a hand-held drilling jig or guide drill having an axial bore there through, so as to enable the external receiver to align with the internal or coupled receiver, the positioning device further comprising a guide pin insertable into the axial bore and adapted to be engaged by the drill chuck of said drill when the perceived axes of the first and second receivers are aligned so as to enable the guide pin to be advanced by the drill along a path of travel in alignment with the internal location.

In an advantageous embodiment, the said first receiver or internal sensor unit is embedded in a unit or handle to which the implanted device is attached. The location and orientation of the receiver relative to each internal concealed location to be positioned can be known through either physical measurement or electronic determination using a calibration routine.

In an advantageous embodiment, the said first receiver or internal unit includes a protective cover. Preferably, the protective cover comprises a plastic casing advantageously shaped to match or conform to the internal shape of the particular intramedullary device being implanted. Thus the embodiment of the invention involves the provision of a locating arrangement that can be used with any commercial nail.

In an advantageous embodiment, the perceived position of the first and second receiver, or additional receivers, relative to the transmitter, can be electronically offset by the connected computer so as to provide a perceived location and axis in space, relative to the sensors. The advantage of this embodiment is that the position and axis of the transverse holes can be ascertained without the sensor being physically at the location. With both the first and second sensors offset to the same position, an axis and location of the transverse hole can be located and a drill or pin passed through the hole without interference from the sensor.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates the components of the invention and positioning of an interlocking nail 120 in the medullary canal of a bone 110.

FIG. 2 illustrates the coordinate axis for the transmitter 104 and receiver 107.

FIG. 3 illustrates the intramedullary nail

FIG. 4 illustrates the nail driver and associated components

FIG. 5 illustrates the drill guide and drill sleeves

FIG. 6 illustrates the displacement vectors of the receiver 107 and receiver 109 and axis offset positions to the transverse hole 121 and axis of drill guide hole 132, respectively, relative to transmitter coordinate origin 201.

FIG. 7 illustrates the calibration tool used with the grill guide and intramedullary nail.

FIG. 8a illustrates the application of the invention with the receiver positioned within a probe inserted in the intramedullary nail.

FIG. 8b illustrates the cross section of different shaped probe heads complimentary to the intended implant 120.

FIG. 9 illustrates the components of the probe when used with a circular cross section implant.

DESCRIPTION OF THE PREFERRED EMBODIMENTS OF THE INVENTION

A first component, such as an orthopaedic implant, and more particularly an intramedullary nail is provided with at least one connector receiving mechanism. In the case of an intramedullary nail, the connector can be a screw and the connector receiving mechanism can be holes in the nail. A drill guide member, is used to guide a drill bit towards a selected hole in the nail.

The drill bit is positioned and oriented by the drill guide member relative to the intramedullar nail. The guiding system includes:

(a) a direct current magnetic field transmitting member; (b) at least one magnetic field receiving means for receiving the transmitted direct current magnetic fields; (c) power means for supplying direct current electrical signals to the transmitting means for creating the transmitted direct current magnetic fields; (d) receiver electronics for measuring, and converting output signals from the magnetic field receiver electronics into position and orientation measurements; and (e) programmed computer, the programmed computer having a visual display member, the output signals from the receiver electronics being converted into position and orientation measurements and visually displayed on the computer visual display member.

The first component is fixed to either the transmitting member or the receiving means. Similarly, the drill guide member is fixed to either a transmitting member or a receiving means. Preferably, the system employees a single transmitter, and both the drill bit guide member and the intramedullary nail are provided with receivers. Thus, the relative position and orientation of the first member relative to the drill guide member can be determined.

The intramedullary nail has a proximal end and a distal end. A support member, such as a handle, is releasably secured to the proximal end of the nail and carries a receiver.

The transmitter for transmitting direct current magnetic fields comprises a core and a multiplicity of roughly orthogonal antenna axis wire windings. The receiver of the transmitted direct current magnetic fields comprises a multiplicity of roughly orthogonal antennae axes that are sensitive to transmitted direct current magnetic fields.

The method of securing an implant, such as an intramedullary nail into a bone includes the steps of inserting the implant into a bone, drilling a hole in the bone proximate the screw receiving hole in the nail, by using a drill member and a drill guide. The determination of the position and orientation of the drill member relative to the holes involves (a) transmitting a direct current magnetic field from a transmitting member, receiving the transmitted direct current magnetic fields at at least one magnetic field receiver. The nail is fixed to either of the transmitting member or the receiving means, preferably, the receiver. Similarly the drill guide is fixed to either a transmitting member the receiving means, preferably, the receiver. The received direct current magnetic fields are converted into position and orientation data in a programmed computer, and displayed on the computer screen. By viewing a virtual representation of the nail and the drill member on the computer screen, the drill member can be moved to the desired location relative to the intramedullary nail.

Advantageously, the nail receiver can be remote from the screw receiving hole so that the receiver need not be carried into the bone along with the nail. The computer program calculates the offset from the receiver to the hole, and thus, the display shows the position of the hole relative to the drill.

In FIG. 1, the nail 120 has been driven into the bone 100 from the right side, and the nail has in the vicinity of its left, i.e. distal end 125 a pair of transverse holes 121 and 121 and in the vicinity of its right, i.e. proximal, end a transverse or oblique hole 121" for receiving transverse bolts 326, 326 and 326", FIG. 3, respectively.

Next, the exact position of the respective drilling axis 321 of a most distal hole 121 in the intramedullary nail 120 is to be determined. This drilling axis can be definitely determined by a linear connecting line of the two center points 322 and 323 on this axis. In order to place a drilling jig 131 in a position aligned with this axis, the two points 322 and 323 on the drilling axis of the distal hole 121 must be located accordingly, and the axis of the drilling jig 532 must be oriented in accordance with these points, whereupon the hole (bore) may be formed in the bone immediately.

The apparatus according to the invention is used for locating the axis 321 generated by these two center points 322 and 323.

The electromagnetic position and orientation measuring system, as described in U.S. Pat. Nos. 4,945,305 and 4,849,692, consisting of: a transmitter driver circuit within an electronic control unit 102 for providing a controlled amount of DC current to each of two or three axes of transmitter 104 one at a time. The amount of DC current provided by driver the signal processing electronics 102 to the transmitter to which 104, via connection 106, is controlled by the computer 101. The transmitter 104 is usually located within a few feet of distance from a patient's leg.

In FIG. 2, transmitter 104 consists of three individual antennae (x202, y203, and z204 axis, FIG. 2) arranged concentrically which generate a multiplicity of DC magnetic fields that are picked up by receiver 107 and receiver 109, (FIG. 1). Each of the receivers 107 and 109 are also composed of three antennae (x, y, and z axis antennae). Receivers 107 and 109 measure not only the fields generated by transmitter 104 but also the earth's magnetic field to thereby effect an ultimate measurement of the position and orientation of the object to which it is attached. The transmitter antennae represent a Cartesian coordinate system 105 with an origin 201 located at the center of transmitter 104 and having three orthogonal axes; an X axis 202, a Y axis 203 and a Z axis 204. Likewise, each receiver 107 and 109 have receiving antennae which represent a Cartesian coordinate system 210 and 220, respectively. The coordinate system 210 of receiver 107 has an origin 211 located at the center of receiver 107 and having three orthogonal axes; an X axis 212, a Y axis 213, and a Z axis 214. The coordinate system 220 of receiver 109 has an origin 220 located at the center of receiver 109, shown in FIG. 5A and having three orthogonal axes; an X axis 222, a Y axis 223, and a Z axis 224.

Receiver 107 and 109 consists of three or two axes, 210, 220, respectively, with driving and detecting circuits that are sensitive to DC magnetic fields. The DC signal output from receiver 107 goes to the signal processing electronics 102 via connection 108. Signal processing electronics 102 controls, conditions, and converts analog receiver signals into a digital format that can be read by computer 101. Computer 101, by way of an algorithm, computes the position and orientation of receiver 107 and 109 with respect to transmitter 104. Computer 101 then outputs this information to a graphic image controller by which the surgeon can view the relative position of the guide 131 with respect to the nail driver 140 and thus to the axis 321 of hole 121 of FIG. 3A.

As illustrated in FIG. 4, receiver 107 is mounted on, or is embedded in, a driver unit 140 used to implant the nail 120 in the bone 100. The nail driver 140 is comprised of a handle 401 and longitudinal body 402. The longitudinal body 402 has a longitudinal cylindrical bore 404 with central axis 403 which is coincident with the longitudinal axis of the intramedullary nail when attached securely to the nail using the specific nail attachment 141 and connecting bolt 142 and locking nut 143.

Nail attachment 141 has an indentation or similar means to align with the protrusion 40 and 406' or other mechanism on end 405 of the longitudinal body 402. Nail attachment 141 has a central bore 415 extending the longitudinal axis of the attachment coincident with the central axis 403. The nail attachment has protrusions 411, on the end opposite from the end having indentations 413, and 413' to provide alignment of the attachment with the indentations 325 located on the proximal end 124 of intramedullary nail 120, as shown in FIG. 3A.

A connecting bolt 142 comprised of threaded end 410, body 423, and threaded end 421 is used to fasten and align the nail 120 with the nail driver 140. Bolt end 410 is formed to mate with the threads 324 on the proximal end 124 of the nail 120. The attachment spacer 141 is slid over the bolt 142 by placing the bolt 142 through the central bore 415. The nail driver 140 is likewise slid over the bolt 142 by placing the bolt 142 through the cylindrical bore 404 of nail driver body 402 such that the protrusions 406 and 406' interlock with indentations 413 and 413', respectively. With the spacer 141 engaged with the nail 120 and nail driver 140 engaged with the spacer 141, internal bore 414 of the locking nut 143 is threaded on threads 421 of the connecting bolt 142.

Receiver 109 is preferably attached to, or embedded in a hand-held guide 131 as illustrated in FIGS. 5A and 5B. Guide 131 is constructed to receive an outer sleeve 134 within the bore 525 of the drill guide hole 132. The outer sleeve 134 is a modified T shape having a end section 541 with a greater diameter than the longitudinal section 542. A central bore 543 is dimensioned to receive the longitudinal section 532 of the inner drill sleeve 133, with the end section 531 prevent complete insertion into the bore 543. The inner drill sleeve 133 has a central bore 533 enabling drill bit 135 to be coincident with the longitudinal axis 532 when drill sleeve 134 is inserted in bore 525.

The controlling computer 101, by way of an algorithm, is able to electronically transpose, both in translation and rotation, the axis 220 and x 222, y 223, and z 224 axes, to a new location of offset axis 520 such that the offset coordinate axis can be located on the longitudinal axis 521. The computer then computes the position and orientation of the offset axis 520 with respect to transmitter 104. Computer 101 then outputs this information to a graphic image controller by which the surgeon can view the relative position of the longitudinal axis 521, as viewed as cross-hairs 112 in FIG. 1, with respect to the nail driver 140, as viewed as cross hairs 111, in FIG. 1, and thus to the axis 321 of hole 121 on the computer display.

Likewise the computer 101 by way of an algorithm, is able to electronically transpose, both in translation and rotation, the nail driver's receiver axis 210 to the offset coordinate axis 310, shown in FIG. 3B such that the offset coordinate axis can be located on the axis 321 of hole 121. The computer then computes the position and orientation of the offset axis 310 with respect to transmitter 104. Computer 101 then outputs this information to a graphic image controller by which the surgeon can view the relative position of the drill guide axis 532 (cross-hairs 112) with respect to this offset axis 310 and corresponding x, y, and z axes and thus to the axis 321 of hole 121 (cross hairs 111).

The mathematical relationship for the distance from the offset axis of the transverse hole 310 to the offset axis 520 of the drill guide 131 can be derived from the position vectors (small letters in bold). FIG. 6 presents a schematic of the position vectors of the system. T is the location of transmitter axis 104 (0,0,0) from which the positions, r1 to the axis S1 210 (x1, y1, z1) of the sensor 107 embedded in the nail holder 140, and r2 to the axis, S2 220, of the sensor 109 embedded in the drill guide 131 are measured electronically by the computer 101 and electronic control unit 102. Likewise the orientation of the offset axes, S1' 310 and S2' 520, are determined relative to the sensor axes, S1 210 and S2 220. The transverse hole to be drilled has an axis S1' 310 which is physically positioned, r1'-r1 from S1 210. This offset position vector, r1'-r1, is determined at the time of surgery, prior to implantation, as part of the calibration procedure. This value will be dependent upon the length of the nail chosen as well as the orientation of the transverse hole. The drill guide hole in the drill guide has an axis S2' 520 which is offset from sensor axis S2 220 by a distance r2'-r2. The offset position vector, r2'-r2 is a constant which is determined from the manufacturing of the drill guide unit 131 and stored in the software. Therefore knowing the above vectors, the vector, r2'-r1' can be determined from the vector relationships:

(r2'-r1')=r2-r1+(r2'-r2)-(r1'-r1)

The software algorithm stored in the computer 101 will provide the relative distance and orientation of the offset holder axis to the nail's transverse hole which in turn can be viewed on the computer monitor by the user.

Procedure for using the Device

The distance and orientation, as depicted by the vector (r2'-r2, FIG. 6) of the axis of the drill guide hole 532 relative to the drill guide sensor 109 are constant and known. However the distance from the receiver 107 in the driver to the axis 321 of the intended hole 121 will be dependent upon the length of the intended implant 120 as chosen by the surgeon. Thus prior to insertion, the distance and orientation of the transverse hole(s) 121 relative to the holder receiver 107 must be determined. This can be performed in a simple "calibration" procedure.

The computer 101 determines the position of the receiver 107 relative to the transmitter 104, but it is desirable to know the position of the axis 321 of the transverse hole 121 relative to the holder sensor. A "calibration" must be performed to determine the offset distance, vector r1'-r1, from the holder receiver 107 to the axis 321 of the transverse hole 121. An alignment pin 700, as illustrated in FIG. 7, is composed of an initial cylindrical segment 705 which is of such diameter or complimentary shape as to fit into bore 535 or bores 533 or 543 of the drill sleeve 133 or 134, respectively. The pin 700 has a central section 710, and a third section 715 which is of such diameter or complimentary shape as to fit into holes 121 and 122. The initial segment 705 is placed in the drill guide bore 535. The third section 715 is inserted in the first of the nail's transverse holes 121. Thus the alignment pin 700 longitudinal axis 721 causes the axis of 521 to be coincident with axis 321. Thus the location of the drill guide offset axis 520, S1' is now known relative to the drill guide receiver axis 210, S2, and thus to the transmitter 104 and the nail driver receive 107, S1. With the alignment tool pin 700 in place, the location and axis of the transverse hole axis 321 relative to the nail driver receiver 107 is computed using an algorithm and digitally stored by the computer 101. The alignment pin 700 and drill guide 131 is moved to the second transverse hole 121' and it's location and axis 321' relative to the nail driver 140 is likewise computed and stored in the computer 101. The procedure is repeated for any additional locking holes in the nail such that the computer has stored the location and axis of each transverse locking hole relative to the handle sensor. Thus the relative distance and orientation of each transverse hole, relative to the sensor in the nail driver is known and the computer has digitally stored the offset coordinates of each hole in the nail for finding the hole after the nail has been implanted.

After the hole locations are stored in the computer 101, the nail 120 is inserted into the bone 100. The computer program then prompts the surgeon to place the drill guide 131 at the first hole location 121. A stationary three dimensional cross-hair 111, representing the position of the axis 321 of the desired transverse hole 121 is displayed on the computer monitor. A second three dimensional cross hair 112 is displayed on the monitor which represents the location and orientation of the drill guide axis 521 relative to the offset axis 310 of the desired transverse hole 121. The surgeon then moves the drill jig until the guide's cross hairs 112 are aligned with the stationary cross hairs 111 on the monitor. The axis of the drill guide 521 is now aligned with the axis 321 of the transverse hole of the nail. The drill guide 131 is held firmly in this orientation or gently taped to set it in the bone 100, a drill bit 135 is inserted in the drill sleeve 133 and drilled through the nail hole 121. The drill bit 135 is removed and a screw 326 inserted to lock the nail with the bone. The computer is then programmed to proceed to the second hole 121' and the procedure repeated. The procedure is repeated until all the holes have been locked.

In a further embodiment of the invention, as illustrated in FIG. 8, receiver 107 is be embedded within a probe head 805, connected to probe 810. The electrical connection for receiver 107 would be contained within probe 810 and connect to the signal processing unit 102 via wire 108. Correspondingly differently shaped probe heads 805 are required for different nail diameters or different profile (cross-sectional) shapes of the nail, FIG. 8b, respectively, to ensure that during insertion of the probe head 805 that the probe head 805 does not rotate relative to the nail 120 such that the orthogonal axes 210 of the receiver 107 remains along the orthogonal axes of the nail 120.

The exact orientation of the receiver 107 at the distal end of the probe head 805 in the longitudinal direction of the nail 120 relative to the axis of the transverse hole 321 is obtained by the fact that the spacing of the transverse hole 121 from the proximal end 124 of the nail 120, with a realistically pronounced deformation and in consideration of the elastic deformability of the probe 810 in the shank thereof, is maintained with a sufficient degree of accuracy. For varying lengths of nails or for the various distal holes 121 or 121' of the nail 120, a stop member 812 needs to be positioned to or fixed to the proximal end 124 of the nail 120 as well as on the probe shank 810 in correspondingly different positions prior to inserting the probe head 805 into the nail 120. This can be done through the use of stop member locking screw 814 or other means known in the art. The probe shank 810 would have gradation markings corresponding to the distance from the proximal end of nail 120 to the hole axis 321 minus a specified setback distance to place the probe head 805 and receiver 107 proximal to the hole 121 to ensure that the probe head 805 is not compromised during the drilling procedure.

The DC signal output from receiver 107 goes to the signal processing electronics 102 via wire 108 which controls, conditions, and converts analog receiver signals into a digital format that can be read by computer 101. Computer 101, by way of an algorithm, computes the position and orientation of receiver 107 with respect to transmitter 104, the position and orientation of receiver 109.

The position of the drill guide 131 relative to the transmitter 104 is likewise computed using the DC signal output from receiver 109 via connection 110 the signal processing electronics 104 and displayed on the computer's 101 display device. The distance and orientation of the axis of the guide receiver 109 relative to the axis 521 of the hole in the drill guide 131 will be equal to a predetermined set back distance of the origin of the axis 210 of the probe head receiver 107 from the hole axis 321 or 321'. Therefore the relative position of the axis of the drill guide 521 with respect to the axis of the nail hole 321 can be visualized on the computer display. Upon alignment of the axes, a drill 135 is passed through the bone 100 and nail hole 121 and withdrawn. A screw or locking bolt 326 is inserted in through the drilled hole and nail.

After performing the above operations at the most distal hole 121, a second bolt 326' is placed into the corresponding hole (bore) 121' using the same procedure.

After performing the above operations at the distal end, the proximal bolt 326" is to be placed into the corresponding hole (bore) 121", and this operation need not be described in greater detail here since, owing to the small distance to the proximal end of the spike, a conventional location and drilling device as described in the referenced patents may be used with a sufficient degree of precision for the locating of the proximal holes.

It should be noted further that the apparatus is capable of operating effectively even if the probe head cannot be guided by the inner profile of the implant, such as, for example, in the case of nails having a circular cross-section. In such instance, auxiliary measures may be taken in order to align or orient the probe head relative to the transverse hole. For example, this may be effected with the aid of a holding device adapted to engage into the hole. FIG. 9 shows a method by which the probe head 805 has finger extensions 905 and 905' with prongs 910 and 910', respectively, and such prongs are able to engage the near edge of holes 121 and 122, respectively, thus provide a rotational and longitudinal position of the probe relative to the hole. The length of the probe extension in addition to the radius of the hole can be made equal to the distance from the axis of receiver 109 and the axis 521 of the drill guide bore 535.

LIST OF COMPONENTS OF THE INVENTION

100 Bone 101 Computer including monitor, cpu, keyboard, other devices 102 Electronic control unit and driver circuit 103 Wires connecting 101 with 102 104 Three axis transmitter 105 Coordinate axis of transmitter 104 106 Wires connecting 102 with 105 107 Receiver sensor in nail driver 125 108 Wires connecting 102 with 107 109 Receiver sensor in drill guide 131 110 Wires connecting 102 with 109 111 Stationary crosshairs representing nail hole axis 310 112 Crosshairs representing drill guide axis 520 120 Intramedullary nail 121 Locking hole in 120 122 Locking hole connected to hole 121 along axis 321 in 120 124 Proximal end of nail 120 125 Distal end of nail 120 131 Drill guide with embedded receiver sensor 109 132 Drill guide hole 133 Inner drill sleeve 134 Outer drill sleeve 135 Drill bit 140 Nail driver 141 Attachment spacer 142 Interlocking shaft 143 Locking nut 201 Origin of transmitter coordinate axis 105 202 X-axis of coordinate axis 105 203 Y-axis of coordinate axis 105 204 Z-axis of coordinate axis 105 210 Receiver 107 coordinate axis 211 Origin of receiver coordinate axis 210 212 X-axis of coordinate axis 210 213 Y-axis of coordinate axis 210 214 Z-axis of coordinate axis 210 220 Receiver 109 coordinate axis 222 X-axis of coordinate axis 220 223 Y-axis of coordinate axis 220 224 Z-axis of coordinate axis 220 310 Offset coordinate axis of axis 210 321 Axis of hole 121 322 Center of hole 121 323 Center of hole 122 324 Means of attachment (threads) at end 124 325 Alignment indentation on end 124 401 Handle of nail driver 140 402 Body of nail driver 140 along the longitudinal axis of nail 120 403 Longitudinal axis of nail driver segment 402 404 Cylindrical bore along axis 403 405 End of segment 402 for attachment with 141 406 Alignment protrusion on end 405 for alignment with attachment spacer 141 410 End of 141 for attachment with proximal end 124 of nail 120 411 Protrusion on end 410 for mating with indentation 325 on proximal nail end 124 413 Indentation on end 412 for mating with protrusion 406 414 Threaded internal bore of locking nut 143 415 Longitudinal bore through spacer 141 421 Threaded end of 142 for attachment with 324 423 Connecting member of 142 connecting end 411 with end 412 520 Coordinate offset axis of center of drill hole 132 and coincident with axis 521 521 Longitudinal axis of drill hole 132 531 End section of drill sleeve 133 532 Longitudinal section of drill sleeve 133 533 Internal bore of drill sleeve 133 535 Bore within drill guide 131 for drill sleeve 133 541 End section of drill sleeve 134 542 Longitudinal section of drill sleeve 134 543 Internal bore of drill sleeve 134 700 Alignment tool 705 end of alignment tool intended to coincide with drill guide bore 533 or drill sleeve bore 710 central section of alignment tool 700 715 end of alignment tool 700 intended to coincide with nail hole 121-122 along axis 321 721 longitudinal axis of alignment tool 700 805 Probe head with embedded receiver 107 810 Probe shank attached to probe head and containing wire 108 812 Stop member 814 Stop member locking screw 905 Probe extension 910 Probe extension prong

Claims

1. A method of securing an implant into a bone using a targeting device having at least a first and a second magnetic field communication units, said first and second communication units being at least one receiver, said receiver receiving multi-axis pulsed direct current magnetic signals in each of three orthogonal planes, and at least one transmitter, said transmitter transmitting multi-axis pulsed direct current magnetic signals in each of three orthogonal planes, a programmed computer having a visual display for displaying relative spatial orientations, comprising the steps of:

A) placing a first of said communication units carried in a fixed position by a drill guide,

B) inserting an implant into a bone, said implant having at least one connector means for receiving a connector to secure said implant to said bone, said connector means being in a fixed position relative to a second of said communication units,

C) determining the position and orientation of said drill guide relative to said connector receiving means, by

(a) transmitting a pulsed direct current magnetic signal from said transmitting unit;

(b) receiving said transmitted pulsed direct current magnetic signal at one of said at least two communication units, said magnetic signals providing the position and location of said communication units in relation to one another;

(c) converting received pulsed direct current magnetic signals into a relative position and orientation data into a format read by said programmed computer;

(d) displaying said converted relative position and orientation data on said programmed computer visual display member,

D) aligning said drill guide with said connector means by viewing a virtual representation of said position and orientation of said connector means and said drill guide as indicated on said visual display member, and

E) drilling a hole in said bone in alignment with said connector means.

2. The method of claim 1, wherein said implant has a proximal end and a distal end, and further comprising the steps of:

A. supporting said proximal end of said implant by a support member releasably secured to said proximal end, said support member,

B. transmitting said magnetic signals or receiving said transmitted magnetic signals from a communication unit in a fixed position proximate said support member and transmitting said magnetic signals or receiving transmitted magnetic signals from a communication unit in a fixed position proximate said drill guide,

wherein said step of converting received pulsed direct current magnetic signals into position and orientation data in a programmed computer includes the step of calculating an offset for the position difference between said position proximate said support member and said position proximate said connector receiving means.

3. The method of claim 2, wherein said magnetic signals are transmitted by said a first and a second communication units and received by a third unit.

4. The method of claim 1, wherein said transmitted magnetic signals are received at said communication unit at a fixed position proximate said support member and at said communication unit at a fixed position proximate said drill guide, said magnetic signals being transmitted from a third communication unit.

5. The method of claim 1, wherein said pulsed direct current magnetic signals are transmitted by a core and a multiplicity of roughly orthogonal antenna axis wire windings.

6. The method of claim 1, wherein said pulsed transmitted direct current magnetic signals are received at a multiplicity of roughly orthogonal antennae axes that are sensitive to transmitted direct current magnetic fields.

7. The method of claim 1, wherein said pulsed direct current magnetic signal are transmitted by a core and a multiplicity of roughly orthogonal antenna axis wire windings and said transmitted pulsed direct current magnetic signals are received at a multiplicity of roughly orthogonal antennae axes that are sensitive to transmitted pulsed direct current magnetic signal.