EP3938797A1

EP3938797A1 - Method and signal-transmitting arrangement for carrying out signal detection by means of magnetic particle imaging

Info

Publication number: EP3938797A1
Application number: EP20711879.5A
Authority: EP
Inventors: Volkmar Schulz; Sebastian Reinartz; Dennis Pantke; Florian MÜLLER
Original assignee: Rheinisch Westlische Technische Hochschuke RWTH
Current assignee: Rheinisch Westlische Technische Hochschuke RWTH
Priority date: 2019-03-15
Filing date: 2020-03-13
Publication date: 2022-01-19
Also published as: WO2020187764A1; DE102019106665A1; US20220167866A1

Abstract

The invention relates to a method for carrying out signal detection by means of magnetic particle imaging, in which method magnetic/magnetisable particles (4), arranged in the field-free region of a location-dependent magnetic field, in particular a gradient magnetic field, are magnetised by means of an excitation magnetic field that changes over time, and the harmonics (9, 15), generated by the particles (4), of the frequency of the excitation magnetic field are detected as a signal from the magnetic particles (4) by means of a receiver coil arrangement (1) which in particular surrounds the particles (4), wherein a signal-transmitting arrangement, which has an outer coil (10) and at least one inner coil (11; 16, 17) connected in series to said outer coil, is positioned within the receiver coil arrangement (1) around the particles (4), wherein the signal received from the particles (4) by the at least one inner coil (11; 16, 17) is transmitted to the outer coil (10) by current flow and is re-emitted by said outer coil, in particular as a result of which the signal (S) received directly from the particles (4) and the signal (S) received from the particles (4) indirectly by the outer coil (10) are superimposed at the receiver coil arrangement (1). The invention also relates to a signal-transmitting arrangement for a magnetic-particle-imaging scanner/spectrometer, comprising an outer coil (10) which in particular has a smaller diameter than the sample-receiving channel (2) of the scanner/spectrometer, and comprising at least one inner coil (11; 16, 17) which is arranged in the outer coil (10), preferably arranged coaxially therein, and in particular has greater diameter than a sample to be examined, wherein the outer coil (10) and the inner coil (11; 16, 17) are electrically connected in series. The invention also relates to a system comprising a magnetic-particle-imaging scanner and a signal-transmitting arrangement.

Description

Method and signal transmission arrangement for carrying out a

Magnetic Particle Imaging Signal Acquisition

The invention relates to a method for carrying out magnetic particle imaging signal detection. The invention also relates to a

Signal transmission arrangement for use in such a signal acquisition.

With the principle of Magnetic Particle Imaging (MPI), concentrations of magnetic or at least magnetizable particles, in particular nanoparticles, such as e.g. preferably iron oxide, can be measured in an examination volume. The particles can e.g. as a tracer, similar to a contrast agent, for

Tissue examinations of living beings are used. Iron oxide in particular has the advantage of being easily degradable in the organism of the living being. The technology thus represents an alternative, or at least a supplement to magnetic resonance tomography or nuclear medicine procedures

In the terminology of this technology, the examination volume is also referred to as “Field-Of-View = FOV”.

In this basically known technique, the magnetic / magnetizable particles arranged in the field-free region of a location-dependent magnetic field, in particular a gradient magnetic field, are magnetized by means of an excitation magnetic field that changes over time. The excitation magnetic field, which changes over time with the sign of the field direction, is superimposed with the location-dependent magnetic field.

The location-dependent magnetic field can be generated, for example, by permanent magnets, but in particular also by electromagnets. The excitation magnetic field is usually generated by electromagnets, preferably by means of current-carrying coils which are fed by a power source in order to generate the excitation magnetic field by means of alternating currents that vary over time. The location-dependent The magnetic field and the varying magnetic field can also be generated in a common coil arrangement. By shifting the field-free area, the total examination volume is formed. The shift can be purely mechanical, electrical or combined.

The field-free region is the local area in which, in the case of the location-dependent magnetic field and / or the superposition of the location-dependent

Magnetic field and varying magnetic field changes the field direction, so it is singularly "zero" and the field strength in the surrounding area is still below the saturation field strength of the particles used. The field-free region is therefore not field-free everywhere in spite of the designation in the relevant terminology. The signal contributions of the particles, however, only come from this region, which is designated as field-free, since the particles are only there in the excitation field

let magnetize.

Outside the field-free region, the magnetization of the particles is saturated and cannot be changed in the excitation magnetic field. The field-free region is at usual

Scanner assemblies as in the invention, especially in scanner devices that are already commercially available, often a line or a point, whereby these terms are not to be understood in the sense of mathematical accuracy, but rather describe the spatial extent of a specific measurement volume. These areas are referred to in the relevant terminology as FFP - field free point or FFL - field free line.

Due to the non-linear magnetization of the particles, their changes

Magnetization not only with the fundamental frequency of the excitation magnetic field, but also with the frequency of higher harmonics, in particular odd harmonics of the excitation frequency. The particles in turn generate alternating magnetic fields with the excitation frequency and the harmonics, the harmonics being able to be discriminated from the excitation frequency by measurement technology and thus the amplitude or intensity of the harmonics is a measure of the concentration of the particles in the field-free area.

A signal that is detected by the magnetized particles is therefore usually a physical variable that represents the amplitude / intensity of the harmonics, including the excitation frequency, for example, an induced voltage or other variables formed therefrom. The technique of MPI imaging, like the invention, thus provides for the signal to be acquired by means of a receiving coil arrangement, in particular which surrounds the particles. The signal is usually recorded in the time domain and converted into the frequency domain by means of Fourier transformation in order to measure the signal components of the Flarmonian.

The coil arrangement that is also used to generate the varying excitation magnetic field, as well as a separate coil arrangement can be used as the receiving coil arrangement.

Known MPI scanners, e.g. from Bruker, include one

Sample receiving channel, which is surrounded by the coils for excitation and signal acquisition. Such a sample receiving channel has a defined size, which in this respect also includes the maximum size of samples that can be examined, e.g. Living beings limited.

Frequently, investigations are made on particles in samples that are significantly smaller than the maximum diameter of the sample receiving channel. The

The magnetic field strength of the harmonics generated by the particles must be detected in such devices with the receiving coil arrangements that are arranged around the outside of the sample receiving channel. So the removal of the

Reception coil arrangement of the particles larger than actually necessary.

This is problematic because the magnetic field strength drops significantly with the radial distance from the particles, in particular with r ³ , as a result of which the signal yield is reduced.

In commercial MPI scanners, a separate receiving unit is provided to reduce the distance between the receiving coil and the particles in the case of samples that are significantly smaller than the receiving channel diameter

Reception coil arrangement and downstream measured value acquisition in the

Use the sample receiving channel and then the measurement value acquisition with this receiving unit instead of the original receiving coil arrangement and

To use the measuring unit of the device. Such a solution generates high costs for this double measuring system.

The object of the invention is therefore to provide a method and a

Provide signal transmission arrangement that allow using a existing receiving coil arrangement to detect signals from the magnetized particles with a higher yield. Preferably, the measuring electronics arranged downstream of an existing receiving coil arrangement should continue to be used for measured value acquisition.

This object is achieved with a method of the type mentioned at the outset, in which furthermore within the receiving coil arrangement, preferably within one that is present in a commercial MPI scanner, around the particles a signal transmission arrangement comprising an outer and at least one connected in series inner coil is positioned.

Such a signal transmission arrangement can preferably be pushed into the sample receiving channel as a passive structural unit, that is to say without an additional external voltage supply. As a result, the at least one inner coil can surround a sample lying in the channel at a smaller radial distance than is the case with the receiving coil arrangement.

According to the invention, the signal received from the alternately magnetized particles with the at least one inner coil is transmitted to the outer coil by current flow and radiated from it again. Namely, the alternating magnetic field generated by the particles initially generates an induced voltage in the at least one inner coil, which generates the current flow that also occurs through the series-connected outer coil, which in turn generates a magnetic field.

The magnetic field generated by the outer coil is in turn closer to the receiving coil in the radial direction and is in turn controlled by it, e.g. as induced voltage. Overall, the signal transmission between the particles and the receiving coil arrangement can thus be improved in a purely passive manner.

The signal received directly from the particles and the signal received indirectly from the outer coil of the particles are preferably superimposed on one another at the receiving coil arrangement.

This is the case even if the inductances of the signal transmission arrangement should result in a time shift between the magnetic field generated by the particles and the magnetic field emitted again by the external coil uncritical, since at least in the frequency domain there is a constructive superposition of the directly and indirectly received harmonic signal components.

A signal transmission arrangement according to the invention for a magnetic particle imaging scanner thus has an outer coil, in particular which is smaller in diameter than the sample receiving channel of the existing scanner, and

at least one inner coil arranged in the outer coil, preferably arranged coaxially therein, in particular which is larger in diameter than a sample to be examined, the outer and the at least one inner coil being electrically connected in series. The at least one inner coil is therefore always smaller in diameter than the outer coil and leaves in its interior or in the interior of a coil carrier on which the at least one inner coil

is wound, a free channel-shaped cross section of the

Signal transmission arrangement in which a sample with particles can be positioned.

The method and the signal transmission arrangement can provide in a preferred embodiment that the signal transmission arrangement by means of a

Capacitor arrangement, which is connected in series with the outer and the at least one inner coil, is tuned resonantly. Such

Capacitor arrangement can comprise one or more capacitors.

The vote can be done by changing the capacitors of the

Capacitor arrangement and preferably take place by means of a capacitor arrangement with variable capacitance.

The coordination can take place in such a way that the frequency range of the Flarmonian to be detected is transmitted better by the coil arrangement than that

Excitation frequency, in particular so that the excitation frequency in the

Coil arrangement of the signal transmission arrangement is damped. The absorption of energy from the magnetic field with the excitation frequency can thus be reduced. The vote can preferably take place in such a way that the elected

The resonance frequency is greater than the excitation frequency, preferably at least 10 times, more preferably at least 20 times greater. In an exemplary

The excitation frequency of the time-varying excitation magnetic field of 25 kFIz, the resonance frequency can be adjusted to 600 kFIz, for example. The capacitor arrangement is further preferred outside the

Excitation magnetic field arranged. This can e.g. be realized in that the capacitor arrangement by means of a cable connection, e.g. through a

Coaxial cable or a twisted pair line is arranged at a distance from the coils. Even more preferably, the capacitor arrangement is arranged in a separate shielding housing, which is positioned outside a sample receiving channel of an MPI scanner. The cable connection can preferably be at least as long as the insertion depth of the signal transmission arrangement

Sample receiving channel is.

In the signal transmission arrangement, the outer coil and the at least one inner coil, in particular the single inner coil, can preferably be arranged on a common coil carrier. The dimensions of the coil carrier can be configured in such a way that its outer diameter, or the outer diameter of the entire arrangement, is smaller than one

Sample receiving channel of an existing MPI scanner with which the method is to be used. The inner free diameter of the

The signal transmission arrangement can be selected such that it is larger, preferably only slightly larger, than a sample to be surrounded with the particles. The common coil carrier can be divided into an outer coil carrier for the outer coil and at least one inner coil carrier for a respective inner coil. The outer and inner coil carriers can be designed in one piece with one another or form separate coil carriers, in particular which can be plugged into one another, preferably can be fastened into one another.

In a possible first embodiment of the respective inner and outer coil, these can each be arranged around a longitudinal axis of the coil

Conductor winding be formed with a pitch of the winding in the direction of the longitudinal axis. Such a respective coil thus forms an arrangement which is also referred to as a solenoid, in particular which forms a cylindrical metal coil which acts like a bar magnet when current flows through it.

In particular in this aforementioned embodiment, the axial length of the outer coil and / or the inner coil, preferably the number of turns of the outer and / or respective inner coil, preferably the length or the

Number of turns correspond to the receiver coil arrangement of the MPI scanner to be used.

However, the invention can also have different designs of a respective inner and / or outer coil.

In a second possible embodiment, it can preferably be provided that an inner and / or an outer coil each comprises two coil parts which are connected in series with one another and are arranged opposite one another, in particular 180 degrees opposite one another, in particular around a longitudinal axis, preferably which corresponds to the longitudinal axis of the signal transmission arrangement or the coil carriers contained therein and corresponds to the longitudinal axis of the sample receiving channel during operation. The connecting line between the midpoints of both coil parts can cross the longitudinal axis of the sample receiving channel, in particular the sample volume with the particles to be examined.

Each of the two coil parts is preferably designed as a spiral winding of a conductor, the spiral winding not lying in a plane, but rather being bent in a plane perpendicular to the named longitudinal axis, preferably in the shape of a part circle. This corresponds to the idea that the coil part or the spiral winding is bent around a cylinder jacket, preferably a circular-cylinder jacket, and can specifically be achieved in that the spiral winding of the conductor is first made in one plane and then the spiral formed on a cylindrical, preferably circular cylindrical outer surface, e.g. of the inner and / or the outer coil support is applied in a contacting manner. In particular, the winding of the conductor of the respective coil part is thus designed in a spiral shape on a cylinder jacket surface. Two such curved spirals of the conductor are thus opposite one another, i.e. on opposite sides of the cylinder surface. The aforementioned center points can be the center points of the spirals. As mentioned, both spiral-shaped coil parts are electrically connected in series with one another in order to jointly form an inner and / or outer coil.

The series connection can preferably be designed such that the winding direction of the two coil parts in the series connection is the same, preferably the one in a first coil part located centrally in the spiral part of the conductor is connected to the part of the conductor of the second coil part lying outside in the spiral.

Each two such opposing coil parts thus form at least one inner coil and at least one outer coil, which are also connected in series. The coil parts of the inner coil and outer coil lie opposite one another in the same direction, but in particular on different ones

Cylinder jacket radii.

Said opposite position of the coil parts is in a direction which is perpendicular to the longitudinal direction of the sample channel or the coil carrier (inner and outer).

Such an arrangement of a coil has the advantage that the aforementioned solenoid coils can receive signals from a first detection channel, e.g. Signal contributions along the longitudinal axis of the sample channel, which can be defined as the Z axis.

With a coil arrangement according to the opposite coil parts, signal contributions from the particles in a direction perpendicular to the longitudinal axis (Z-axis) can be detected during an examination, e.g. the X direction and / or Y direction.

According to the invention, a signal transmission arrangement has an outer and at least one inner coil. These two coils can be designed either according to the aforementioned first embodiment or according to the aforementioned second embodiment.

However, the invention can also provide that the signal transmission arrangement comprises inner and outer coils according to the first embodiment and additionally at least one arrangement of inner and outer coils according to FIG

aforementioned second embodiment. Signals can be recorded with two or three channels.

In a further possible combined embodiment, it can be provided that the signal transmission arrangement is an arrangement of an outer and

having at least one inner coil according to the first embodiment and two Arrangement of inner and outer coils according to the second embodiment, wherein in the two arrangements the opposite coil parts have crossed, preferably perpendicular directions. For example, one of the arrangements can include signals in the X direction and the other signals in the Y direction, with the solenoid coils detecting signals in the Z direction.

It can be provided that a different one for each of the arrangements

Reception coil arrangement of the MPI scanner is used.

Overall, the invention can thus also implement three-channel signal detection.

With general validity for all possible arrangements of coils, the invention can furthermore provide that the at least one inner coil is moved relative to the outer coil and relative to the particles, in particular during a signal detection sequence. Such a movement can e.g. along a common axis around which the inner and outer coils

are arranged. However, the inner coil can also move freely in space relative to the outer coil. A movement can also take place in such a way that the axis of the inner coil is moved parallel but not coaxially to the axis of the outer coil. Overall, the signal detection of the particles with the inner coil can be optimized through the mobility.

E.g. For this purpose, an inner coil or its coil carrier can be provided by means of a manually operable handle or also an actuator, which the

Manipulation in space enabled. Such a handle or actuator can e.g. also be formed by a catheter or some other instrument with which the inner coil preferably also into the interior of the body of a

Living being, e.g. can be brought into the blood vessels. This can bring about a particularly close proximity to the particles.

In all embodiments, it is preferably provided that the outer coil and the at least one inner coil surround the particles. Especially with the

In the embodiment of a movable inner coil, it can also be provided that the inner coil does not surround the particles, but only the outer one. In the designs of a movable inner coil, this is preferably flexibly connected to the outer coil when it is electrically connected in series.

One possible embodiment can provide that an inner coil carrier, which carries the inner coil, is linearly displaceable to an outer coil carrier with the outer coil, preferably on the same common coil axis. E.g. inner and outer coil carriers can be connected by means of a linear guide system, which allows the linear movement of the coil carriers relative to one another.

In a further development, the invention can also provide that it has at least two inner coils, in particular spaced apart on the same axis, which alternatively can be switched in series with the outer coil by means of a switchover arrangement. A respective inner coil can have its own inner coil carrier that carries the coil. The inner coils can also be arranged on a common inner coil carrier.

Thus, in the method, one of at least two inner coils can optionally be used for signal acquisition. The at least two alternatively switchable coils are preferably each in series with the same capacitor arrangement, so that the same resonance tuning is present for both coils, in particular if both coils are identical in terms of inductance and / or structural design. The invention can also provide that the at least two inner coils can alternatively be switched in series with the same outer coil but in series with a different capacitor arrangement. The resonance frequencies or bandpass properties can thus be the same for the various inner coils, but they can also be designed differently. The at least two alternatively switchable coils can also be designed differently in terms of inductance and / or their construction.

The invention can also provide that the signal transmission arrangement has at least two inner coils which are each connected in series with the same outer coil. In this case, signals from the particles can be detected simultaneously with the at least two inner coils, preferably which can be operated with different resonance. The inner coils can be in series with a common capacitor arrangement, but alternatively also in series with each other

Capacitor arrangement be connected in series. Another capacitor arrangement is understood to mean one with a different capacitance.

The series arrangements of in each case an inner coil and a respective specially assigned capacitor arrangement then preferably form one to one another

Parallel connection, which in turn is in series with the outer coil.

The inductance of the at least two inner coils can be identical, but they can also be designed differently.

The resonance frequencies or bandpass properties can thus be used for the at least two inner coils, in particular due to the different inductances of the coils and / or due to different capacitances of the associated

Capacitor arrangements can also be designed differently.

The at least two inner coils of this embodiment variant can be arranged coaxially one inside the other, in particular completely overlapping, or coaxially one inside the other and axially spaced or also axially spaced next to one another, in particular on the same coil axis.

The invention can e.g. provide to calculate back from the signals of the two or more, preferably axially spaced, inner coils, in particular the electrically and / or structurally identical coils, to the location of the generation of the signals from the particles, in particular to improve the spatial resolution of a scanner.

A further preferred embodiment can provide that the

Signal transmission arrangement comprises a coil carrier with an outer coil and comprises at least one coil carrier with at least one inner coil, which are mechanically and electrically detachable and connectable, in particular wherein the inner coil carrier with the at least one inner coil from a set of several inner coil carriers with different inner diameter Coils, in particular, different inner free diameters can be selected. With this design, for a sample that includes the particles, the inner coil can be selected from the set with the smallest possible diameter.

A further development can also provide that the electrical conductors of the coils can be cooled by means of a coolant guided in the conductors, in particular to dissipate heat loss and / or to cool the superconducting ones

Resistance range. The ladder can e.g. therefore be made hollow and in a fluid circuit of a coolant, e.g. Helium.

The following figures show the prior art and preferred designs.

Figure 1 A: shows a structural design of one known in the prior art

MPI scanners

FIG. 1 B: shows the electrical equivalent circuit diagram for FIG. 1 B

Figure 1 C: shows a signal spectrum of the prior art according to Figure 1 A and

1 B as signal amplitude versus frequency

FIG. 2A: shows a structural design according to the invention in a section perpendicular to the coil axes

Figure 2B: shows the electrical equivalent circuit diagram of the embodiment of Figure 2A

Figure 2C: shows a signal spectrum in comparison to the prior art according to the invention according to Figure 2A / 2B as a signal amplitude against the

frequency

Figure 3A: shows a structural second embodiment according to the invention in

Section parallel to the coil axis

FIG. 3B: shows the electrical equivalent circuit diagram of the embodiment according to FIG. 3A

FIG. 3C: shows the magnetic field strength and thus the detection sensitivity of both coils of the embodiment of FIGS. 3A / 3B against the Z axis, that is to say the coil axis In the figures 1 an embodiment according to the prior art can be seen. In this embodiment, by means of an excitation coil arrangement 1, which is controlled by a driving voltage 5, the time-varying

Excitation magnetic field generated and also with this coil 1 as

Receiving coil arrangement detects the signal of the particles 4. The coil arrangement 1 is located in the radial direction outward behind a cover 2 which defines the sample receiving channel with an inner free diameter. The field-free region is located in the examination volume 3 and can within this

Volume can be varied locally.

The location-dependent magnetic field, in particular the gradient magnetic field for

Generation of a field-free area is assumed here as a given. The means for generating this magnetic field are not further visualized or, in one possible embodiment, could also be provided by the coil arrangement 1 at the same time.

Due to the alternating magnetic field of the excitation coil arrangement 1, the particles 4 in the field-free area of the examination volume 3 become non-linear

magnetized. The magnetization of the particles 4 thus changes with the

Fundamental frequency of the excitation and with higher harmonics of this frequency. FIG. 1 C shows a frequency spectrum of the measured frequencies of the alternating magnetic field generated by the particles 4. Plotted against the frequency f, the signal components S of the fundamental frequency / excitation frequency 8 and the harmonics 9 can be seen here, which can only be clearly assigned to the particles 4 as a signal source.

Figures 2 show a first possible embodiment of the invention. In the same way, the excitation coil arrangement / reception coil arrangement 1 of a e.g. commercial MPI scanner can be seen radially behind the housing / sample receiving channel 2.

In addition, FIGS. 2 show a signal transmission arrangement which is inserted into the sample receiving channel and also the particles 4 in the

Examination volume 3 surrounds. The signal transmission arrangement comprises an outer coil 10, which is smaller in diameter than the sample receiving channel 2 and an inner coil 11, which is smaller in diameter than the outer coil 10, but in particular larger than a sample to be surrounded with the particles 4. Both coils 10 and 11 are electrically connected in series with one another and with a capacitor arrangement 13. The capacitor arrangement 13, which is used for resonance tuning, is laid out with a twisted pair line 14 from the sample receiving channel 2 and arranged in a shielding housing 12. The capacitance value of the capacitor arrangement 13 can be fixed, but it can also be variably adjustable, for example in that it comprises at least one variable capacitor.

Figures 2 make it clear that the inner coil 11 is arranged closer to the particles 4 than the excitation / reception coil arrangement 1 and also closer than the outer coil 10. The magnetic field generated by the particles 4 thus calls an induced voltage in the inner coil 11 In particular, a higher voltage than directly in the coil arrangement 1. This voltage causes a current to flow through the inner coil 11 and outer coil 10, so that the latter in turn generates a magnetic field which also generates an induction voltage in the coil arrangement 1. The induction voltages generated directly and indirectly via the coils 10 and 11 in the coil arrangement 1 are superimposed and have the same frequency components as in FIG. 1 C. In contrast, FIG. 2C shows that the signal amplitude S in the Flarmonian 9 using the Invention compared to the prior art is increased by the signal components 15 due to the better coupling of the magnetic field generated by the particles 4 via the signal transmission device. The signal components 15 increased by the invention are shown here in dotted lines.

FIGS. 3 show a further embodiment in which two inner coils 16 and 17 are used in the signal transmission device according to the invention. Each of the two inner coils 16/17 can alternatively be replaced by a

Switching device 19 can be connected in series with the outer coil 10 and the capacitor arrangement 13.

According to FIG. 3C, the inner coils 16 and 17 have magnetic field strength distributions B along the coil axis Z, which preferably - as shown here - overlap in certain areas and which likewise Represent reception sensitivity distributions for magnetic fields generated by the particles 4 as a function of the coil axis position Z. On the basis of these distributions known for the coils 16, 17, conclusions can be drawn about the position of the particles 4 on the coil axis Z from the signal spectra acquired with the coil 16 on the one hand and, after switching over, with the coil 17,

Local resolution can be improved.

Instead of switching, it is also possible to use one capacitor for each of the coils 16 and 17, so that different

Result in resonance frequencies that allow a simultaneous measurement.

Figures 4 visualize possible versions of the

Signal transmission device with regard to the formation of the inner and outer coils.

FIG. 4A shows a plan view of the Z axis, which is used as the longitudinal axis of the

Sample receiving channel is accepted. The plan view shows the last winding layer of the inner coil 11 and outer coil 10, which are each designed as a solenoid coil, as shown in FIG. 4E, i.e. the windings of the coil conductor take place with a slope around the Z-axis.

In contrast, FIGS. 4B and 4C show inner and outer coils 10, 11. The series connection of the two coil parts is not shown here.

FIG. 4F shows an illustration of each coil part of the two coils 10, 11 in a planar, planar representation. In this illustration, the coil part is as

Spiral winding of the conductor formed. There is one in the application

However, the spiral winding is bent, in particular bent around an imaginary or even concrete cylinder jacket surface, e.g. which are the cylindrical surface of the inner or outer coil support, which are not shown here.

The two respective coil parts are diametrically opposite one another around the Z-axis. Thus, in the opposite of Figure 4C, a channel of the Signal detection in the X direction and, in FIG. 4C, a channel can be detected in the Y direction.

FIG. 4D now shows a total of a signal transmission device in which the coil arrangements of FIGS. 4A, B and C are combined together and arranged around the Z axis. In this arrangement, signal contributions can be recorded in all three directions.

Claims

1. A method for carrying out a magnetic particle imaging signal detection in which a location-dependent magnetic field, in particular a gradient magnetic field, is arranged in the field-free region

magnetic / magnetizable particles (4) are magnetized by means of a time-changing excitation magnetic field and as a signal from the magnetized particles (4) by means of a receiving coil arrangement (1), in particular which surrounds the particles (4), the harmonics generated by the particles (4) (9, 15) the frequency of the excitation magnetic field are detected, characterized in that within the

Receiving coil arrangement (1) around the particles (4) a

Signal transmission arrangement with an outer (10) and at least one inner coil (11; 16,17) connected in series therewith is positioned, the signal received from the particles (4) through the at least one inner coil (11; 16,17) Current flow is transmitted to the outer coil (10) and emitted again by it, in particular as a result of which the signal (S) received directly from the particles (4) and that from the particles (4) indirectly from the outer one at the receiving coil arrangement (1) Coil (10) superimpose received signal (S).

2. The method according to claim 1, characterized in that the

Signal transmission arrangement by means of a capacitor arrangement (13), in particular one whose capacitance is variably adjustable

Capacitor arrangement (13), which is connected in series with the outer (10) and the at least one inner coil (11; 16, 17), is resonantly tuned, in particular to the frequency range of the to be detected

Harmonics (9, 15), in particular for damping the reception of the fundamental frequency (8) of the excitation magnetic field, preferably where the

Capacitor arrangement (13) is arranged outside the excitation magnetic field.

3. The method according to any one of the preceding claims, characterized in that the at least one inner coil (11; 16, 17) is moved relative to the outer coil (10) and relative to the particles (4), in particular during a sequence of signal detection.

4. The method according to any one of the preceding claims, characterized in that one of at least two inner coils (16, 17), in particular those arranged on the same axis at a distance from one another, optionally by means of a switching arrangement (19) in series with the outer coil (10 ) is switched.

5. The method according to any one of the preceding claims 1 to 3, characterized

characterized in that with at least two inner coils, in particular which are tuned to different resonance, signals from the at the same time

Particles are captured.

6. Signal transmission arrangement for a magnetic particle imaging scanner / spectrometer, characterized by an outer coil (10), in particular which is smaller in diameter than the sample receiving channel (2) of the scanner / spectrometer, and at least one in the outer coil (10 ) arranged, preferably coaxially arranged therein, inner coil (11; 16, 17), in particular which is larger in diameter than a sample to be examined, the outer (10) and the at least one inner coil (11; 16,

17) are electrically connected in series.

7. Signal transmission arrangement according to claim 6, characterized in that it is connected to the outer (10) and the at least one inner coil (11; 16, 17) by means of a capacitor arrangement (13), in particular a capacitor arrangement (13) with variable capacitance. connected in series is tunable in the resonance frequency, preferably, the

Capacitor arrangement (13) is arranged at a distance from the coils (10, 11, 16, 17) by means of a cable connection (14), more preferably in a separate shielding housing (12).

8. Signal transmission arrangement according to one of the preceding claims 6 or 7, characterized in that the outer coil (10) and the at least an inner coil (1 1; 16, 17) are arranged on a common coil carrier.

9. Signal transmission arrangement according to one of the preceding claims 6 to 8, characterized in that the at least one inner coil (1 1; 16,

17), in particular its coil carrier part, can be moved relative to the outer coil (10), in particular to its coil carrier part.

10. Signal transmission arrangement according to one of the preceding claims 6 to 9, characterized in that it has at least two, in particular on the same axis (Z) spaced apart inner coils (16, 17), which optionally alternatively by means of a switching arrangement (19) in series with the outer Coil (10) are switchable.

1 1. Signal transmission arrangement according to one of the preceding claims 6 to 9, characterized in that it has at least two inner coils which are simultaneously connected in series with the same outer coil, preferably with a respective inner coil being connected in series with a different capacitor arrangement, in particular where the

Series arrangements of one inner coil and one each

associated capacitor arrangement to each other form a parallel circuit which is in series with the outer coil.

12. Signal transmission arrangement according to one of the preceding claims 6 to 1 1, characterized in that it comprises a coil carrier with an outer coil (10) and at least one coil carrier with at least one inner coil (1 1; 16, 17), the mechanical and are electrically detachable and connectable, in particular wherein the inner coil carrier with the at least one inner coil (1 1; 16, 17) can be selected from a set of several inner coil carriers with inner coils (1 1; 16, 17) of different diameters.

13. Signal transmission arrangement according to one of the preceding claims 6 to 12, characterized in that the electrical conductors of the coils (10, 1 1,

16, 17) can be cooled by means of a coolant guided in the conductors, in particular for the dissipation of heat loss and / or for cooling in the superconducting resistance area.

14. Signal transmission arrangement according to one of the preceding claims 6 to 13, characterized in that the respective inner and outer coil (10,

11) each as arranged around a longitudinal axis of the coil

Conductor winding are formed with a pitch of the winding in the direction of the longitudinal axis, in particular as a solenoid coil.

15. Signal transmission arrangement according to one of the preceding claims 6 to 14, characterized in that an inner and / or an outer coil each comprises two coil parts which are connected in series with one another and are arranged opposite one another, in particular 180 degrees opposite one another, in particular one Longitudinal axis around.

16. Signal transmission arrangement according to claim 15, characterized in that each of the two coil parts is designed as a spiral winding of a conductor, in particular wherein the respective spiral winding is bent in a plane perpendicular to said longitudinal axis, preferably the spiral winding is bent around a cylinder jacket or on a cylinder jacket lies.

17. System consisting of a magnetic particle imaging scanner and a

Signal transmission arrangement according to one of the preceding claims 6 to 16.