Method for constructing a transversal gradient coil in a magnetic resonance imaging system

• US 5,309,107 A
• Filed: 02/05/1993
• Issued: 05/03/1994
• Est. Priority Date: 02/07/1992
• Status: Expired due to Term

• Current Assignee: Siemens AG
• Original Assignee: Siemens AG
• Inventors: Pausch, Guenther
• Primary Examiner(s): Tokar, Michael J.
• Application Number:
  US08/014,220
• Time in Patent Office: 452 Days
• Field of Search: 324/300, 324/307, 324/309, 324/310, 324/311, 324/312, 324/313, 324/314, 324/318, 324/322, 324/319, 128/653.5
• US Class Current: 324/318
• CPC Class Codes: G01R 33/385 using gradient magnetic field coils

Abstract

For the purpose of constructing a transversal gradient coil, formed by a conductor, for producing a target field distribution with a prescribed current in a magnetic resonance imaging system, a series of points defining the locations of the coil conductor on a carrier are identified by placing a grid mesh network of elementary saddle coils over the carrier, calculating the magnetic field of these elementary saddle coils and defining a number of ampere-turns for each elementary saddle coil with a fit algorithm on the basis of the target field distribution. The discrete conductor position points are then identified by integration which, in combination, define the path of the coil conductor on the carrier.

Claims

1. A method for constructing a transversal gradient coil formed by a conductor for producing a target field distribution with a prescribed current in a magnetic resonance imaging system, said method comprising the steps of:

subdividing a surface of a carrier on which said coil is to be disposed by means of a grid mesh network placed over said carrier, said network having grid openings and mesh branches;

occupying each grid opening in said network with a modeled elementary coil in the form of a closed turn, each elementary coil generating a respective magnetic field;

calculating the magnetic field generated by each of said elementary coils;

defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution;

calculating a number of ampere-turns for each mesh branch by superimposing the ampere-turns for all of the elementary coils elements adjacent each mesh branch and thereby obtaining an ampere-turn density distribution over said network;

successively integrating said ampere-turn density distribution over whole-numbers of turns along an integration path based on said prescribed current to obtain a plurality of points on said carrier; and

positioning said conductor on said carrier in a configuration conforming to said points.

2. A method as claimed in claim 1 wherein the step of successively integrating said ampere-turn density distribution is further defined by successively integrating said ampere-turn density distribution over whole-numbers of turns along an integration path based on said prescribed current to obtain a plurality of points on said carrier respectively corresponding to the centers of gravity of said distribution divided into segments defined by said whole-numbers of turns.

3. A method as claimed in claim 2 wherein the step of defining the number of ampere-turns for each elementary saddle coil using a fit algorithm based on said target field distribution is further defined by defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution and on a selected physical boundary condition for optimizing at least one overall behavior characteristic of said gradient coil.

4. A method as claimed in claim 3 wherein said magnetic resonance imaging system includes a cryoshield, and wherein the step of defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution and a selected boundary condition is further defined by using a fit algorithm based on said target field distribution and boundary conditions for correcting field errors due to eddy currents in said cryoshield.

5. A method as claimed in claim 3 wherein said magnetic resonance imaging system includes a cryoshield, and wherein the step of defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution and a selected boundary condition is further defined by using a fit algorithm based on said target field distribution and a boundary condition for minimizing eddy currents in said cryoshield.

6. A method as claimed in claim 3 wherein the step of defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution and a selected boundary condition is further defined by using a fit algorithm based on said target field distribution and a boundary condition for minimizing global bending forces.

7. A method as claimed in claim 3 wherein the step of defining a number of ampere-turns for each elementary coil using a fit algorithm based on said target field distribution and a selected boundary condition is further defined by using a fit algorithm based on said target field distribution and a boundary condition for minimizing mechanical vibration behavior in said magnetic resonance imaging system.

8. A method as claimed in claim 1 wherein the step of occupying each grid opening in said network with a modeled elementary coil in the form of a closed turn is further defined by occupying each grid opening in said network with a modeled elementary saddle coil in the form of a closed turn.