MEANS AND METHOD FOR SENSING A MAGNETIC STRAY FIELD IN BIOSENSORS

Abstract

A magnetic sensor (MS) comprising a magneto-resistive element (GMR) for sensing a magnetic stray field (SF) generated by a magnetizable object (SPB) when magnetized and for generating an electrical object signal (UOB) which depends on the sensed magnetic stray field (SF), the sensor (MS) comprising a magnetic field generator (WR1, WR2) for generating a magnetic field (H, Hext) having a first frequency (ω1) for magnetizing the magnetizable object (SPB), a current source (AC2) for at least generating an AC-current (I2 sin ω2t) having a second frequency (ω2t) through the magneto-resistive element (GMR), and electronic means for generating an electrical output signal (U0) derived from the electrical object signal (UOB), the electronic means comprising stabilization means for stabilizing the amplitude of the electrical output signal (U0), the stabilization means deriving its information which is needed for said stabilization from the amplitude of a signal component, which is present in the object signal (UOB) during operation, which is linearly dependent on the steepness of the magneto-resistive element (GMR), the steepness being defined as the derivative of the resistance of the magneto-resistive element (GMR) as a function of the magnetic field through the magneto-resistive element in a magnetically sensitive direction of the magneto-resistive element (GMR).

Description

The invention relates to a method for sensing a magnetic stray field generated by a magnetizable object when magnetized and for generating an electrical object signal which depends on the sensed magnetic stray field. The invention further relates to a magnetic sensor comprising a magneto-resistive element for sensing the magnetic stray field generated by the magnetizable object when magnetized and for generating the electrical object signal, and to a biochip comprising such a sensor for use in e.g. molecular diagnostics biological sample analysis or chemical sample analysis.

The introduction of micro-arrays or biochips is revolutionizing the analysis of samples for DNA (desoxyribonucleic acid), RNA (ribonucleic acid), nucleic acids, proteins, cells and cell fragments, tissue elements, etcetera. Applications are e.g. human genotyping (e.g. in hospitals or by individual doctors or nurses), medical screening, biological and pharmacological research, detection of drugs in saliva. The aim of a biochip is to detect and quantify the presence of a biological molecule in a sample, usually a solution.

Biochips, also called biosensors, biosensor chips, biological microchips, gene-chips or DNA chips, consist in their simplest form of a substrate on which a large number of different probe molecules are attached, on well defined regions on the biochip, to which molecules or molecule fragments that are to be analyzed can bind if they are matched.

The term “substrate” may include any underlying material or materials that may be used, or upon which a device, a circuit or an epitaxial layer may be formed. The term “substrate” may also include a semiconductor substrate such as e.g. a doped silicon, a gallium arsenide (GaAs), a gallium arsenide phosphide (GaAsP), an indium phosphide (InP), a germanium (Ge), or a silicon germanium (SiGe) substrate. The “substrate” may include, for example, an insulating layer such as a SiO₂ or an Si₃N₄ layer in addition to a semiconductor substrate portion. Thus the term “substrate” also includes glass, plastic, ceramic, silicon-on-glass, silicon-on-sapphire substrates. The term “substrate” is thus used to define generally the elements for layers that underlie a layer or portions of interest. Also the “substrate” may be any other base on which a layer is formed, for example a glass or metal layer.

For example, a fragment of a DNA molecule binds to one unique complementary DNA (c-DNA) molecular fragment. The occurrence of a binding reaction can be detected, e.g. by using fluorescent markers that are coupled to the molecules to be analyzed. As an alternative to fluorescent markers magnetizable objects can be used as magnetic markers that are coupled to the molecules to be analyzed. It is the latter type of markers which the present invention is dealing with. In a biochip said magnetizable objects are usually implemented by so called superparamagnetic beads. This provides the ability to analyze small amounts of a large number of different molecules or molecular fragments in parallel, in a short time. One biochip can hold assays for 10-1000 or more different molecular fragments. It is expected that the usefulness of information that can become available from the use of biochips will increase rapidly during the coming decade, as a result of projects such as the Human Genome Project, and follow-up studies on the functions of genes and proteins. A general explanation of the functioning of the biochip has already been described in the international patent application of the present applicant published as WO 03/054523 A2.

A biochip consisting of an array of sensors (e.g. 100) based on the detection of superparamagnetic beads may be used to simultaneously measure the concentration of a large number of different biological molecules (e.g. protein, DNA) in a sample fluid (e.g. a solution like blood or saliva). The sample fluid comprises a target molecule species or an antigen. Any biological molecule that can have a magnetic label (marker) can be of potential use. The measurement may be achieved by attaching a superparamagnetic bead to the target, magnetizing this bead with an applied magnetic field, and using (for instance) a Giant Magneto Resistance (GMR) sensor to detect the stray field of the magnetized beads.

In the current patent application focus is for a biochip based on excitation of superparamagnetic nanoparticles. However also the application in other magneto resistive sensors like Anisotropic Magneto Resistor (AMR) and Tunnel Magneto Resistor (TMR) is part of the invention. The magnetic field generator may comprise a current flowing in a wire which generates a magnetic field, thereby magnetizing a superparamagnetic bead. The stray field from the superparamagnetic bead introduces an in-plane magnetization component in the GMR, which results in a resistance change.

For further explanation of the background of the invention reference is made to FIGS. 1 and 2.

FIG. 2 shows an embodiment of a magnetic sensor MS on a substrate SBSTR. A single or a multiple of such (a) sensor(s) may be integrated on the same substrate SBSTR to form a biochip BCP as is schematically indicated in FIG. 1. The magnetic sensor MS comprises a magnetic field generator which, in this example, is integrated in the substrate SBSTR e.g. by a first current conducting wire WR₁. It may also comprise a second (or even more) current conducting wire WR₂. Also other means in stead of a current conducting wire may be applied to generate the magnetic field H. The magnetic field generator may also be located outside (external excitation) the substrate SBSTR. In each magnetic sensor MS a magnetoresistive element, for example a giant magnetoresistive resistor GMR, is integrated in the substrate SBSTR to read out the information gathered by the biochip BCP, thus to read out the presence or absence of target particles TR via magnetizable objects thereby determining or estimating an areal density of the target particles TR. The magnetizable objects are preferably implemented by so called superparamagnetic beads SPB. Binding sites BS which are able to selectively bind a target TR are attached on a probe element PE. The probe element PE is attached on top of the substrate SBSTR.

The functioning of the magnetic sensor MS or more generally of the biochip BCP is as follows. Each probe element PE is provided with binding sites BS of a certain type. Target sample TR is presented to or passed over the probe element PE, and if the binding sites BS and the target sample TR match, they bind to each other. The superparamagnetic beads SPB are directly or indirectly coupled to the target sample TR. The superparamagnetic beads SPB allow to read out the information gathered by the biochip BCP. Superparamagnetic particles are ferromagnetic particles of which at zero applied magnetic field the time-averaged magnetization is zero due to thermally induced magnetic moment reversals that are frequent on the time scale of the magnetization measurement. The average reversal frequency is given by

$v=v_0\exp \frac{-\mathrm{KV}}{\mathrm{kT}}$

where KV (with K the magnetic anisotropy energy density and V the particle volume) is the energy barrier that has to be overcome, and ν₀ is the reversal attempt frequency (typical value: 10⁹ s⁻¹), k is the Boltzmann constant, and T is the absolute temperature (in Kelvin).

The magnetic field H magnetizes the superparamagnetic beads SPB which as a response generate a stray field SF which can be detected by the GMR. Although not necessary the GMR should preferably be positioned in a way that the parts of the magnetic field H which passes through the GMR is perpendicular to the sensitive direction of the layer of the GMR. A total external field for which the GMR is sensitive is indicated by H_ext in FIG. 2.

The stray field SF has a horizontal component (the sensitive direction of the layer of the GMR) and will thus generate a difference in the resistance value of the GMR. By this an electrical output signal (e.g. generated by a current change through the GMR when biased by a DC voltage, not shown in FIG. 1) can be delivered by the sensor MS which is a measure for the amount of targets TR.

Not only the amount of superparamagnetic beads but also the total gain of the sensor determines the amplitude of the output voltage of the sensor. Therefore the total gain should be known e.g. by measuring the total gain before the actual bio-measurement. Preferably also this total gain is calibrated to be equal to a desired value. Furthermore it is desirable to perform cross-talk isolation techniques for measuring the effect of the magnetic cross-talk caused by the magnetic field which results directly (thus not via the paramagnetic beads) from the magnetic field generator. The total gain of the sensor is dependent on various elements such as an amplifier (or buffer), and the steepness of the GMR. The steepness is the derivative of the resistance of the magneto-resistive element as a function of the magnetic field through the magneto-resistive element in a magnetically sensitive direction of the magneto-resistive element. Even if cross-talk cancellation is performed any change in the value of the gain of the amplifier or said steepness of the GMR during the bio-measurements can adversely affect the accuracy of the measurement. In this respect the most critical component in the sensor is the GMR. The steepness of the GMR, and therefore the total gain of the sensor, is dependent on parameters which are difficult to control for instance applied magnetic fields, production tolerances, aging effects, and temperature. There is thus a high need to stabilize the sensitivity of the GMR.

It is therefore an object of the invention to stabilize the sensitivity of a GMR present in a magnetic sensor.

In order to achieve this object the invention provides a magnetic sensor comprising a magneto-resistive element for sensing a magnetic stray field generated by a magnetizable object when magnetized and for generating an electrical object signal which depends on the sensed magnetic stray field, the sensor comprising a magnetic field generator for generating a magnetic field having a first frequency for magnetizing the magnetizable object, a current source for at least generating an AC-current having a second frequency through the magneto-resistive element, and electronic means for generating an electrical output signal derived from the electrical object signal, the electronic means comprising stabilization means for stabilizing the amplitude of the electrical output signal, the stabilization means deriving its information which is needed for said stabilization from the amplitude of a signal component, which is present in the object signal during operation, which is linearly dependent on the steepness of the magneto-resistive element.

The invention is based on the insight that by applying the AC-current with the second frequency, the sensed object signal will not only comprise a signal component which depends on the sensed magnetic stray field but will also comprise one or more signal components of which the amplitude is linearly dependent on the sensitivity of the GMR. By the electronic means such a signal component can be isolated from the remainder of the signal in the object signal and gives a measure for the sensitivity of the GMR. This makes it possible to stabilize the total gain.

The AC-current through the GMR causes an internal magnetic field in the GMR. Due to asymmetric current distribution in the GMR stack, the current through the GMR will introduce an in-plane magnetic field component in the sensitive layer of the sensor. This effect can be interpreted as internal magnetic cross talk and will give rise to a voltage component which is linear to the squared amplitude of the AC-current and which is linear to the sensitivity of the GMR. Linear to the squared amplitude of the AC-current also means linear to the second harmonic component (thus having a frequency which is twice as high as the second frequency) in relation to the AC-current. Thus stabilizing the sensitivity of the GMR can be performed by detecting the second harmonic component (in relation to the second frequency) in the object signal and by performing some action to cancel the influence of the previously mentioned difficult to control parameters. Other harmonic components, e.g. the fourth harmonic component, can be used in stead of the second harmonic. However since generally the second harmonic is predominately present it is preferred to use the second harmonic in view of reaching the highest possible signal-to-noise ratio in the sensor and thus in reaching the highest accuracy for the bio-sensor measurements.

The invention may further be characterized in that the stabilization means comprises means for generating a further AC-current, having a third frequency, through the magneto-resistive element, and in that the signal component is a harmonic component in the current through the magneto-resistive element having a frequency which is equal to the third frequency, or to the difference of the third and the second frequency, or to the sum of the third and the second frequency. The further AC-current is preferably generated by the presence of a further magnetic field generator for generating the further magnetic field. Sometimes the earlier mentioned in-plane magnetic field component is very weak and as a consequence the second harmonic component is also very weak. This makes detection of the second harmonic component very difficult. It may result in a too noisy signal thereby negatively influence the accuracy of the bio-measurement. By the addition of the further magnetic field, signal components in the object signal are generated having frequencies equal to the third frequency, or to the difference of the third and the second frequency, or to the sum of the third and the second frequency. All these signal components are linearly dependent to the sensitivity of the GMR and can be isolated, individually or combined, and used to stabilize the total gain of the sensor in a corresponding manner as previously explained with reference to the detection of the second harmonic component.

One way of stabilizing the sensitivity of the GMR is by adding steepness adaptation means for adapting the steepness of the magneto-resistive element. This may for instance be performed by changing the value of the DC-current through the magneto-resistive element. Alternatively the adaptation of the steepness is performed by changing a DC value component in the further magnetic field e.g. by changing a DC component in the further DC-current. The gain adaptation means may comprise a synchronous detector for synchronously detecting the signal component, and means for comparing the detected signal component with a target value for the steepness of the magneto-resistive element and for delivering an error signal as a result of the comparison. The error signal changes the DC value of the current through the GMR or in the further magnetic field (or further current). By doing so a negative feedback loop is created in which the error signal will be controlled to be equal (or close) to zero. As a consequence the sensitivity of the GMR will be made equal to the target value (and is thus stabilized).

Another way of stabilizing the sensitivity of the GMR is by adding gain adaptation means for adapting a gain value in the electronic transfer from the electrical object signal to the electrical output signal. Since now there is no negative feedback loop in which the GMR is incorporated, it is easier to design than the previous mentioned way because undesired oscillations or overshoot can not occur. The gain adaptation means may comprise a synchronous detector for synchronously detecting the signal component, and means for comparing the detected signal component with a target value for the steepness of the magneto-resistive element and for delivering a control signal as a result of the comparison. This control signal is used for the changing of the gain value.

In another embodiment, superparamagnetic beads are applied to the reference-sensor during production. This can be achieved by either e.g. spotting (like ink-jet spotting) a well defined surface density concentration of beads or a well defined volume density of beads.

These beads may be utilized for calibration of the transfer function. If the sensor is shielded for free moving beads in the sample fluid, which is the case if the bead coverage is large enough, the transfer function may also be stabilized during the actual bio-measurement.

In another embodiment the sensitivity of the GMR is controlled by varying the strength of the magnetic field produced by an external magnet or by varying the position of the external magnet by translation or rotation.

The electronic means may comprises a further synchronous detector for synchronously detecting the object signal, or a gain adapted version of the object signal, on the first frequency and/or on the difference of the first and the second frequency, and/or on the sum of the first and second frequency, and a frequency low pass filter for filtering the resulted signal from the further detector and for delivering the electrical output signal as a result of the filtering. By this the electrical output signal is a pure DC-signal which is a measure for the amount of targets TR and thus for the concentration of biological molecules in the sample fluid.

As an alternative the gain of the reference sensor is obtained by measuring the response to at least one field generating wire in the vicinity of the reference sensor. It is important to be not sensitive to the beads on the reference sensor surface or into the solution as the number of beads may fluctuate during the bio-measurement and disturb the stabilization mechanism. Therefore preferably magnetic beads are avoided near the reference sensor surface by omitting binding regions on the surface, by proper shielding, by pulling beads away from the sensor or by measuring at a frequency above the response bandwidth of the super paramagnetic beads. As an alternative beads are attracted in a well defined way to the sensor surface. The advantage of this method is that it may shield the reference sensor from free moving beads above the sensor, which avoid said beads to influence on the stabilization mechanism of the GMR. The attracting forces may be generated by a magnetic field gradient introduced by magnetic field generating wires near the sensor.

If desired, after attracting beads to the surface, beads near the surface are removed by (magnetically) washing it away. As an alternative beads are applied to the reference sensor during production. This can be achieved by either e.g. spotting (like ink-jet spotting) a well defined surface density concentration of beads or a well defined volume density of beads. These beads may be used for gain stabilizing during the bio-measurement. Preferably said beads shield the magnetic field from free moving beads in the sample fluid. As an alternative the response of paramagnetic beads are “switched off”. As a consequence only magnetic cross-talk is measured which can be used to stabilize the total gain. This can be done by applying a vertical magnetic field, e.g. having frequency ω₃ above the magnetic response frequency of the beads, perpendicular to the sensitive direction of the GMR. This field saturizes the beads, as a consequence only the magnetic cross-talk from the current wires are measured. This signal is indicative for the gain, and can thus be used to keep the gain constant. It can also be done by applying beads with hysteresis (with the aid of an additional magnetic field). The beads are adjusted to their linear region, which is necessary for detection. If then the additional field is taken away, the beads will no longer respond to the magnetic field, and thus only cross-talk is then measured.

The invention also provides a method for stabilizing the steepness of a magneto-resistive element in a magnetic sensor for sensing a magnetic stray field generated by a magnetizable object when magnetized and for generating an electrical object signal which depends on the sensed magnetic stray field comprising the steps of:

generating a magnetic field, having a first frequency, for magnetizing the magnetizable object,

generating an AC-current, having a second frequency, through the magneto-resistive element,

generating an electrical output signal from the electrical object signal, and

stabilizing the amplitude of the electrical output signal by detecting a signal component which is present in the object signal and which is linearly dependent on the steepness of the magneto-resistive element.

The invention further provides a biochip comprising an inventive magnetic sensor. The biochip may comprise a multiple of magnetic sensors wherein at least one inventive sensor is used as a reference sensor and wherein the adaptation of the steepness of the magneto-resistive elements or the gain adaptation means for adapting the gain value in the electronic transfers from the electrical object signals to the electrical output signals in the other sensors is performed by using information derived from the reference sensor.

Preferably the sensitivity of the GMR is measured in the same frequency range as the beads excitation is performed. By doing so the highest signal-to-noise ratio can be reached. Optionally the sensor may comprise a so called Wheatstone bridges or half-Wheatstone bridges in which one or more GMRs are incorporated.

The invention will be further elucidated with reference to the accompanying drawings, in which:

FIG. 1 shows a biochip comprising a substrate and a plurality of magnetic sensors,

FIG. 2 shows an embodiment of a magnetic sensor with integrated magnetic field excitation;

FIG. 3 shows the resistance of a GMR as a function of the magnetic field component in the direction in which the layer of the GMR is sensitive to magnetic fields;

FIG. 4 shows part of a magnetic sensor in which besides the magnetic field from the beads also the internally generated field generated by the GMR itself is illustrated for explanatory reasons;

FIG. 5 shows a schematic of an inventive embodiment in which means are present for adapting the DC-current through the GMR;

FIG. 6 shows a cross-section of a GMR stack in which the current through the stack is schematically indicated;

FIG. 7 shows a schematic of an inventive embodiment which comprises gain adaptation means for adapting the gain value in the electronic transfer from the electrical object signal to the electrical output signal;

FIG. 8 shows a schematic of an alternative inventive embodiment for adapting the gain value;

FIG. 9 schematically shows an example of an advantageous location for a wire for generating the further magnetic field having the third frequency;

FIG. 10 shows a schematic of an inventive embodiment in which means are present for adapting the DC-current through the GMR and in which the further magnetic field having the third frequency is present;

FIG. 11 shows a schematic of an inventive embodiment which comprises gain adaptation means for adapting the gain value in the electronic transfer from the electrical object signal to the electrical output signal and in which the further magnetic field having the third frequency is present;

FIG. 12 shows a schematic of an inventive embodiment, as an alternative for the embodiment as shown in FIG. 10, in which the DC-value in the further magnetic field is adapted; and

FIGS. 13 and 14 show an array of sensors in which one inventive sensor acts as a reference sensor and in which the steepness of the GMRs in the other sensors is stabilized with the help of information derived from the reference sensor.

The drawings are only schematic and non-limiting. In the drawings the size of some of the elements may be exaggerated and not drawn on scale and serve only for illustrative purposes. The description to the Figures only serve to explain the principles of the invention and may not be construed as limiting the invention to this description and/or the Figures.

FIG. 3 shows the resistance of the GMR as a function of the magnetic field component H_ext. It is to be noted that the GMR sensitivity

$s_{\mathrm{GMR}}=\frac{R_{\mathrm{GMR}}}{H_{\mathrm{ext}}}$

is not constant but depends on H_ext. It is also depends on any internally generated magnetic field caused by asymmetric current distribution in the GMR stack.

In the sensor MS as shown in FIG. 2, in stead of the giant magnetoresistive GMR any other means which have a property (parameter) which depends on magnetic field such as certain types of resistors like a tunnel magnetoresistive (TMR) or an anisotropic magnetoresistive (AMR) can be applied. In an AMR, GMR or TMR material, the electrical resistance changes when the magnetization direction of one or more layers changes as a result of the application of a magnetic field. GMR is the magnetoresistance for layered structures with conductor interlayers in between so-called switching magnetic layers, and TMR is the magneto-resistance for layered structures comprising magnetic metallic electrode layers and a dielectric interlayer.

In GMR technology, structures have been developed in which two very thin magnetic films are brought very close together. A first magnetic film is pinned, what means that its magnetic orientation is fixed, usually by holding it in close proximity to an exchange bias layer, a layer of antiferromagnetic material that fixes the first magnetic film's magnetic orientation. A second magnetic layer or free layer, has a free, variable magnetic orientation. Changes in the magnetic field, in the present case originating from changes in the magnetization of the superparamagnetic particles SPB, cause a rotation of the free magnetic layer's magnetic orientation, which in turn, increases or decreases the resistance of the GMR structure. Low resistance generally occurs when the sensor and pinned layers are magnetically oriented in the same direction. Higher resistance occurs when the magnetic orientations of the sensor and pinned layers (films) oppose each other.

TMR can be observed in systems made of two ferromagnetic electrode layers separated by an isolating (tunnel) barrier. This barrier must be very thin, i.e., of the order of 1 nm. Only then, the electrons can tunnel through this barrier. This is a quantum-mechanical transport process. The magnetic alignment of one layer can be changed without affecting the other by making use of an exchange bias layer. Changes in the magnetic field, in the present case originating from changes in the magnetization of the superparamagnetic particles SPB, cause a rotation of the sensor film's magnetic orientation, which in turn, increases or decreases resistance of the TMR structure.

The AMR of ferromagnetic materials is the dependence of the resistance on the angle the current makes with the magnetization direction. This phenomenon is due to an asymmetry in the electron scattering cross section of ferromagnet materials.

FIG. 4 shows part of a magnetic sensor in which besides the magnetic field H_ext (coming from the beads) also the internally generated field H_int generated by the GMR itself is indicated. A current source I_BIAS which supplies a DC-current I_DC and an AC-current source AC₂ which supplies an AC-current I₂ sin ω₂t having a second frequency ω₂ are coupled to the magneto-resistive element GMR. Thus the sum of these two currents flow through the GMR and is indicated with the sense current i_s. The sense current i_s causes a signal (voltage) U_GMR across the GMR. The voltage U_GMR is amplified by an amplifier AMP which delivers an object signal U_OB. The sense current is generates the internal magnetic field H_int=α·i_sense in the GMR. Therefore by choosing the appropriate value for the sense current i_s the curve shown in FIG. 3 can be “moved” horizontally and a suitable sensitivity of the GMR can be chosen. The effect of the internal magnetic field H_int can be interpreted as internal magnetic cross talk and will give rise to a voltage component e_int=s_GMR·α·i_s² in the signal U_GMR, in which s_GMR is the sensitivity of the GMR and α is a constant value. As a result the GMR voltage contains a second harmonic signal, which is utilized to stabilize the GMR sensitivity. This is illustrated as follows. The total in-plane magnetization H_x in the sensitive layer of the GMR equals H_x=H_ext+H_int=H_ext+α·i_s

The signal U_GMR can be expressed by:

u_GMR=i_s(R_GMR+s_GMR·(H_ext+α·i_s))=i_s(R_GMR+s_GMR·H_ext)+i_s²·s_GMR·α.

By substituting i_s=I_DC+I₂ sin ω₂t:

u_GMR=(I_DC+I₂ sin ω₂t)·(R_GMR+s_GMR·H_ext)+(I_DC²+2I_DCI₂ sin ω₂t+I₂² sin ω₂t)·s_GMR·α

The magnetic field from the beads equals: H_ext=H₁ sin ω₁t

The following expression can then be derived for the signal U_GMR:

$u_{\mathrm{GMR}}=I_{\mathrm{DC}}·\left(R_{\mathrm{GMR}}+s_{\mathrm{GMR}}·\alpha ·I_{\mathrm{DC}}\right)+\frac{1}{2}I_2^2·s_{\mathrm{GMR}}·\alpha +I_2\sin {\omega }_2t·\left(R_{\mathrm{GMR}}+s_{\mathrm{GMR}}·\alpha ·2I_{\mathrm{DC}}\right)+I_{\mathrm{DC}}·s_{\mathrm{GMR}}·H_1\sin {\omega }_1t+\frac{1}{2}I_2·s_{\mathrm{GMR}}·H_1\left[\cos \left({\omega }_1-{\omega }_2\right)t-\cos \left({\omega }_1+{\omega }_2\right)t\right]-\frac{1}{2}I_2^2·s_{\mathrm{GMR}}·\alpha ·\cos 2{\omega }_2t$

The last term in the latter expression for the signal U_GMR equals

$-\frac{1}{2}I_2^2·s_{\mathrm{GMR}}·\alpha ·\cos 2{\omega }_2t$

and is thus a second harmonic component in relation to the second frequency ω₂. Further the sensitivity s_GMR of the GMR is linearly present in this last term. Thus with the aid of this last term the sensitivity can be stabilized. this can be performed by synchronously demodulating the object signal U_OB, which is an amplified version of the signal U_GMR.

The result of this demodulation is a DC component which is proportional to s_GMR and independent from H₁.

FIG. 5 shows a schematic of an inventive embodiment in which means are present for adapting the DC-current through the GMR. In addition to the schematic of FIG. 4 the following elements are present: a first multiplier MP₁, a second multiplier MP₂, a (first) frequency low pass filter LPF₁, a subtracter DFF, and an integrating filter INT. The first multiplier MP₁ synchronously demodulates the object signal U_OB by multiplying the object signal U_OB with a signal cos 2ω₂t. (For simplification the amplitude in this Figure and other Figures is chosen to be equal to “1”, but this may not be interpreted as a restriction.) The resulted signal is a DC-value and is subtracted from a target value s_TR. The resulting error signal is delivered to the integrating filter INT. The output signal of the integrating filter INT is used to adapt the DC-value I_DC of the current source IBIAS. Note that the elements “AMP”, “MP₁”, DFF, “INT”, “IBIAS” form a negative feedback loop. Therefore, if the gain of the feedback loop is sufficiently high, the error signal at the output of the subtracter DFF (=the input of the integrating filter INT) will be controlled to approximately zero. Therefore the effective sensitivity of the sensor will be equal to the target value s_TR (and is thus stabilized). The thus stabilized object signal U_OB is synchronously demodulated by the second multiplier MP₂ which multiplies the object signal U_OB with either cos(ω₁−ω₂)t or cos(ω₁−ω₂)t or sin(ω₁)t, or a combination of these three signals. The resulted signal UMP₂ at the output of the second multiplier MP₂ is filtered by the low pass filter LPF₁ and delivers the electrical output signal U₀ which is a pure DC-signal and which is a measure for the amount of targets TR (see FIG. 2) and thus for the concentration of biological molecules in the sample fluid.

FIG. 6 shows a cross-section of a GMR stack in which the current through the stack is schematically indicated. The previous mentioned parameter α and s_GMR both are a function of the current distribution in the GMR stack. FIG. 6 shows the current distribution in the GMR stack, which is centered in the nonmagnetic layer NML between the free (sensitive) layer FL and the pinned layer PL. Moving the center of gravity of the sense current i_s to an optimal position just below the sensitive layer FL, results in more magnetic field strength being induced by the sense current i_s in the sensitive layer FL, which increases the control range and the gain of the stabilizing circuitry. This can be achieved by optimizing the resistance balance in the stack, e.g. by adding a low-ohmic layer to the stack or by changing the thickness of the different layers in the stack.

The applied magnetic field H_int (see FIG. 5), generated by the sense current i_s, is concentrated in the GMR, so that there is a neglectable interaction between the magnetic beads SPB (see FIG. 2) near the sensor surface and the applied sensor current. Therefore this method can be applied simultaneously with the actual magnetic bead measurement.

Note that the harmonic distortion components due to the non-linear GMR characteristic are neglectable because of the small AC amplitude of the magnetic field induced by the sense current i_s.

FIG. 7 shows a schematic of an inventive embodiment which comprises gain adaptation means for adapting the gain value in the electronic transfer from the electrical object signal U_OB to the electrical output signal U₀. The circuit of FIG. 7 differs from the circuit of FIG. 5 in the following. The integrating filter INT and the subtracter DFF are not present, and thus there is no feedback loop. Thus also the DC-value I_DC of the current source IBIAS is not controlled by an error signal. Further the circuit of FIG. 7 comprises, in addition to the circuit of FIG. 5, a gain adapter G_ADPT which is with a signal input coupled to the output of the amplifier AMP for receiving the object signal U_OB and with a signal output coupled to an input of the second multiplier MP₂ for delivering the signal U_OBG which is a gain adapted version of the object signal U_OB. Further the circuit of FIG. 7 comprises, in addition to the circuit of FIG. 5, a further frequency low pass filter LPF₂ which is coupled between the output of the first multiplier MP₁ and a control input of the gain adapter G_ADPT. The circuit operates as follows. The object signal U_OB is multiplied (synchronously demodulated) with a signal cos 2ω₂t like in the circuit of FIG. 5. The resulted signal is filtered by the further low pass filter LPF₂ which delivers a control signal to the control input of the gain adapter G_ADPT. By the presence of the further low pass filter LPF₂ this control signal is a pure DC-signal. The control signal is compared to the target value s_TR which is present at a reference input of the gain adapter G_ADPT. The gain of the gain adapter G_ADPT is expressed by the following equation:

$\frac{U_{\mathrm{OB}}}{U_{\mathrm{OBG}}}=\frac{s_{\mathrm{TR}}}{G+\delta }$

in which G is the value of the DC-signal delivered by the further low pass filter LPF₂, and is thus related to the sensitivity s_GMR of the GMR, and δ determines the maximum possible gain of the gain adapter G_ADPT. Thus, like in the circuit of FIG. 5, the effective sensitivity of the sensor is stabilized. The advantage of the circuit of FIG. 7 over the circuit of FIG. 5 is that now no feedback loop is present and thus with respect of the stability (avoiding overshoot and oscillations) this circuit is easier to design and does not depend on the sense current dependent gain controlling property of the GMR. In stead of the indicated location in FIG. 7 the gain adapter G_ADPT may also be located after the second multiplier MP₂.

FIG. 8 shows a schematic of an alternative inventive embodiment for adapting the gain value. The circuit of FIG. 8 differs in construction with the circuit of FIG. 5 in the following. In FIG. 8 a third multiplier MP₃ is with a first input coupled to the output of the amplifier AMP and with an output coupled to a common connection point of the first and second multipliers MP₁ and MP₂. Further in the circuit of FIG. 8 the output of the integrating filter INT is not coupled to the current source IBIAS but to a second input of the multiplier MP₃. It is to be noted that although the construction of the circuit of FIG. 8 shows a large resemblance with the construction of the circuit of FIG. 5 the principle of operations of these two circuits are different. The principle of operation of the circuit of FIG. 8 is similar to the principle of operation of the circuit of FIG. 7. Basically the (negative) feedback loop formed by the elements: “MP₃”, “MP₁”, “DFF”, “INT” in FIG. 8 perform a similar function as the feedforward loop formed by the elements: “MP₁”, “LPF₂”, “G_ADPT” in FIG. 7. It is to be noted that although the circuit of FIG. 8 comprises a feedback loop possible complication for the design with respect to stability, like in FIG. 5, is not to be expected since this feedback loop contains less elements in the loop; the current source IBIAS and the GMR are not present in the feedback loop.

FIG. 10 shows a schematic of an inventive embodiment in which means are present for adapting the DC-current through the GMR and in which a further magnetic field H₃ sin ω₃t having the third frequency ω₃ is present. The constructional difference of the circuit of FIG. 10 with the circuit of FIG. 5 is the presence of a further magnetic field generator implemented by a further AC-current source AC₃ and a further wire WR₃. The further AC-current source AC₃ supplies the further AC-current I₃ sin ω₃t through the further wire WR₃ which as a response generates the further magnetic field H₃ sin ω₃t. Application of the circuit of FIG. 10 is advantageous in all situations in which the internally generated magnetic field H_int is so small that it is difficult (too noisy signal) to accurately detect the second harmonic component in the object signal U_OB. (Note that the arrow below H_int=α·i_s intentionally indicated smaller than in the previous Figures.) So basically an AC-current having a frequency ω₃ is induced in the GMR and takes over the function of the second harmonic component. Thus harmonic components having frequencies equal to ω₃−ω₂ and to ω₃+ω₂ occur in the current through the GMR. As a consequence these components are also present in the signal U_GMR across the GMR and in the object signal U_OB. The operation of the circuit is further similar to that of the circuit in FIG. 5 except for the fact that the object signal U_OB is now not synchronously detected on a frequency 2ω₂ but on either ω₃−ω₂, ω₃+ω₂, or ω₁. This is performed by the first multiplier MP₁ which multiplies the object signal U_OB with either cos(ω₃−ω₂)t, cos(ω₃+ω₂)t, sin ω₁t, or a combination of these three signals.

FIG. 9 schematically shows an example of an advantageous location for the further wire WR3 for generating the further magnetic field H₃ sin ω₃t. Because the further wire WR₃ is located below the GMR the further magnetic field does not (or hardly) reach the superparamagnetic beads SPB. This is because the GMR forms a shield for the further magnetic field. Further also the distance from the further wire WR₃ to the superparamagnetic beads SPB is relatively large compared to the distance from the beads to the GMR.

As an alternative to the location of the wire WR₃ in FIG. 9 the wire WR₃ may also be located adjacent to the GMR. Now the beads SPB are closer to the wire WR₃, so that the beads SPB may disturb the measurement of the sensitivity S_GMR of the GMR. This effect can be suppressed by measuring the sensitivity S_GMR at a frequency well above the response bandwidth of the magnetic beads SPB, thus at a frequency

${\omega }_3\ge \frac{1}{{\tau }_{\mathrm{neel}}}.$

The time constant τ_neel is the so-called Neel relaxation time (see for Neel relaxation: “Journal of Magnetism and Magnetic Materials 194 (1999) page 62 by R. Kötiz et al.)

Generally speaking: by increasing ω₃, the response from the super paramagnetic beads SPB will decrease. By sweeping ω₃ over a broad frequency range, information about the gain and the sensitivity of the magnetic sensor and thus about the number of beads SPB is retrieved.

As an alternative a wire WR₃ adjacent (or below the GMR) generates a DC magnetic field in order to control the sensitivity s_GMR. This approach will probably generate a non-neglectable field gradient, which may actuate beads SPB. Generating the DC field only during gain stabilization and during the bio-measurement (measuring the response from the beads) can minimize this effect.

As yet another alternative the sensitivity s_GMR is controlled by varying the strength or the position (translation, rotation) of an external magnet (permanent or electromagnet) with respect to the biochip.

It is also possible that the external magnet also generates a fluctuating magnetic field in the GMR in order to perform the measurement of the sensitivity s_GMR.

FIG. 11 shows a schematic of an inventive embodiment which comprises gain adaptation means for adapting the gain value in the electronic transfer from the electrical object signal U_OB to the electrical output signal U₀ and in which the further magnetic field generator having the third frequency ω₃ is present. Basically the construction of this circuit is similar to the circuit of FIG. 7 but with the addition of the further magnetic field generator comprising the wire WR₃, and the AC-current source AC₃. The addition of the further magnetic field generator is for the same reasons as mentioned earlier with reference to FIG. 10.

FIG. 12 shows a schematic of an inventive embodiment, as an alternative for the embodiment as shown in FIG. 10, in which the DC-value in the further magnetic field is adapted by adapting an addition DC-current source which supplies a DC-component I_DC3 through the wire WR₃ in stead of adapting the DC-current source I_BIAS.

FIGS. 13 and 14 show an array of sensors in which one inventive sensor acts as a reference sensor RFS and in which the steepness of the GMRs in the other biosensor arrays BSA is stabilized with the help of information derived from the reference sensor RFS. The DC sense current i_s of each sensor is corrected by the same gain correcting value. β represents the detection of the second harmonic of the sense current i_s in the reference sensor RFS. The output of loop filter α, which represent the gain correcting value, controls the amplitude of the DC sense current in each sensor. It is assumed that the GMR gain variations are the same for each sensor in the array. This is a good assumption since the sensors are located close to each other on the same biochip. As an alternative to the system of FIG. 13 the system of FIG. 14 comprises wires (coils) which generate adaptable DC-magnetic fields towards the respective GMRs for controlling the GMRs (in stead of controlling the GMRs by adapting the DC-currents through the GMRs).

It should be noted that the above-mentioned embodiments illustrate rather than limit the invention, and those skilled in the art will be capable of designing alternative embodiments without departing from the scope of the invention as defined by the appended claims. In the claims, any reference signs placed in parentheses shall not be construed as limiting the claims. The words “comprising” and “comprises”, and the like, do not exclude the presence of elements other than those listed in any claim or in the application as a whole. The singular reference of an element does not exclude the plural reference of such elements. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures can not be used. Any terms like top, bottom, over, under and the like in the description and the claims are used for descriptive purposes and not necessarily for describing relative positions. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other orientations than described or illustrated by the Figures.

Claims

1. A magnetic sensor (MS) comprising a magneto-resistive element (GMR) for sensing a magnetic stray field (SF) generated by a magnetizable object (SPB) when magnetized and for generating an electrical object signal (UOB) which depends on the sensed magnetic stray field (SF), the sensor (MS) comprising a magnetic field generator (WR1, WR2) for generating a magnetic field (H, Hext) having a first frequency (ω1) for magnetizing the magnetizable object (SPB), a current source (AC2) for at least generating an AC-current (I2 sin ω2t) having a second frequency (ω2) through the magneto-resistive element (GMR), and electronic means for generating an electrical output signal (U0) derived from the electrical object signal (UOB), the electronic means comprising stabilization means for stabilizing the amplitude of the electrical output signal (U0), the stabilization means deriving its information which is needed for said stabilization from the amplitude of a signal component, which is present in the object signal (UOB) during operation, which is linearly dependent on the steepness of the magneto-resistive element (GMR), the steepness being defined as the derivative of the resistance of the magneto-resistive element (GMR) as a function of the magnetic field through the magneto-resistive element in a magnetically sensitive direction of the magneto-resistive element (GMR).

2. A sensor as claimed in claim 1 characterized in that the signal component is the second harmonic component, in relation to the second frequency (ω2), in the AC-current through the magneto-resistive element (GMR).

3. A sensor as claimed in claim 1 characterized in that the stabilization means comprises means (AC3) for generating a further AC-current (I3 sin ω3t), having a third frequency (ω3), through the magneto-resistive element (GMR), and in that the signal component is either a harmonic component in the current through the magneto-resistive element (GMR) having a frequency which is equal to the third frequency (ω3), or to the difference (ω3−ω2) of the third and the second frequency, or to the sum (ω3+ω2), of the third and the second frequency.

4. A sensor as claimed in claim 3 characterized in that the sensor comprises a further magnetic field generator (WR3) for generating a further magnetic field (H3 sin ω3t), having the third frequency (ω3), for causing the generation of the further AC-current.

5. A sensor as claimed in claim 1 characterized in that the stabilization means comprises steepness adaptation means for adapting the steepness of the magneto-resistive element.

6. A sensor as claimed in claim 5, characterized in that the adaptation of the steepness is performed by changing the value of a DC-current through the magneto-resistive element.

7. A sensor as claimed in claim 4 characterized in that the stabilization means comprises steepness adaptation means for adapting the steepness of the magneto-resistive element wherein the adaptation of the steepness is performed by changing a DC value component in the further magnetic field.

8. A sensor as claimed in claim 6, characterized in that the steepness adaptation means comprises a synchronous detector (MP1) for synchronously detecting the signal component, and means for comparing the detected signal component with a target value (sTR) for the steepness of the magneto-resistive element and for delivering an error signal as a result of the comparison, and in that the error signal forms a basis for the changing of the value of the DC-current through the magneto-resistive element or the DC value component in the further magnetic field.

9. A sensor as claimed in claim 1, characterized in that the stabilization means comprises gain adaptation means (GADPT) for adapting a gain value in the electronic transfer from the electrical object signal to the electrical output signal.

10. A sensor as claimed in claims 9, characterized in that the gain adaptation means comprises a synchronous detector (MP1) for synchronously detecting the signal component, and means for comparing the detected signal component with a target value (sTR) for the steepness of the magneto-resistive element and for delivering a control signal as a result of the comparison which forms a basis for the changing of the gain value.

11. A sensor as claimed in claim 1 characterized in that the electronic means comprises a further synchronous detector (MP2) for synchronously detecting the object signal (UOB), or a gain adapted version of the object signal (UOBG), on the first frequency and/or on the difference of the first and the second frequency, and/or on the sum of the first and second frequency, and a frequency low pass filter (LPF1) for filtering the resulted signal from the further detector (MP2) and for delivering the electrical output signal (U0) as a result of the filtering.

12. A biochip (BCP) comprising a magnetic sensor as claimed in claim 1.

13. A biochip comprising a multiple of magnetic sensors wherein at least one sensor as claimed in claim 1 is used as a reference sensor (RFS) and wherein the adaptation of the steepness of the magneto-resistive elements or the gain adaptation means for adapting the gain value in the electronic transfers from the electrical object signals to the electrical output signals in the other sensors (BSA) is performed by using information derived from the reference sensor (RFS).

14. A method for stabilizing the steepness of a magneto-resistive element in a magnetic sensor for sensing a magnetic stray field generated by a magnetizable object when magnetized and for generating an electrical object signal which depends on the sensed magnetic stray field, the steepness being defined as the derivative of the resistance of the magneto-resistive element as a function of the magnetic field through the magneto-resistive element in a magnetically sensitive direction of the magneto-resistive element, comprising the steps of:

generating a magnetic field, having a first frequency, for magnetizing the magnetizable object,

generating an AC-current, having a second frequency, through the magneto-resistive element,

generating an electrical output signal from the electrical object signal, and

stabilizing the amplitude of the electrical output signal by detecting a signal component which is present in the object signal and which is linearly dependent on the steepness of the magneto-resistive element.